WO2012112698A2 - Implants articulaires adaptés à un patient et améliorés, procédures et outils destinés à déterminer, évaluer, corriger, modifier et/ou s'adapter à une variation et/ou à une asymétrie anatomique - Google Patents

Implants articulaires adaptés à un patient et améliorés, procédures et outils destinés à déterminer, évaluer, corriger, modifier et/ou s'adapter à une variation et/ou à une asymétrie anatomique Download PDF

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Publication number
WO2012112698A2
WO2012112698A2 PCT/US2012/025274 US2012025274W WO2012112698A2 WO 2012112698 A2 WO2012112698 A2 WO 2012112698A2 US 2012025274 W US2012025274 W US 2012025274W WO 2012112698 A2 WO2012112698 A2 WO 2012112698A2
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WO
WIPO (PCT)
Prior art keywords
patient
implant
bone
component
medial
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Application number
PCT/US2012/025274
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English (en)
Other versions
WO2012112698A3 (fr
Inventor
Raymond A. Bojarski
Philipp Lang
Nam Chao
Wolfgang Fitz
John Slamin
Daniel Steines
Thomas Minas
Terrance Wong
Original Assignee
Conformis, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
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Publication date
Application filed by Conformis, Inc. filed Critical Conformis, Inc.
Priority to AU2012217654A priority Critical patent/AU2012217654B2/en
Priority to CN201280018695.5A priority patent/CN103476363B/zh
Publication of WO2012112698A2 publication Critical patent/WO2012112698A2/fr
Publication of WO2012112698A3 publication Critical patent/WO2012112698A3/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/38—Joints for elbows or knees
    • A61F2/3859—Femoral components
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/14—Surgical saws ; Accessories therefor
    • A61B17/15—Guides therefor
    • A61B17/154—Guides therefor for preparing bone for knee prosthesis
    • A61B17/157—Cutting tibia
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/16—Bone cutting, breaking or removal means other than saws, e.g. Osteoclasts; Drills or chisels for bones; Trepans
    • A61B17/17—Guides or aligning means for drills, mills, pins or wires
    • A61B17/1739—Guides or aligning means for drills, mills, pins or wires specially adapted for particular parts of the body
    • A61B17/1764—Guides or aligning means for drills, mills, pins or wires specially adapted for particular parts of the body for the knee
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/3094—Designing or manufacturing processes
    • A61F2/30942—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/38—Joints for elbows or knees
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/38—Joints for elbows or knees
    • A61F2/3804—Joints for elbows or knees for elbows
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/40—Joints for shoulders
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/42—Joints for wrists or ankles; for hands, e.g. fingers; for feet, e.g. toes
    • A61F2/4202—Joints for wrists or ankles; for hands, e.g. fingers; for feet, e.g. toes for ankles
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/14—Surgical saws ; Accessories therefor
    • A61B17/15—Guides therefor
    • A61B17/154—Guides therefor for preparing bone for knee prosthesis
    • A61B17/155—Cutting femur
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/3094—Designing or manufacturing processes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/44—Joints for the spine, e.g. vertebrae, spinal discs
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/3094—Designing or manufacturing processes
    • A61F2/30942—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques
    • A61F2002/30948—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques using computerized tomography, i.e. CT scans
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/3094—Designing or manufacturing processes
    • A61F2/30942—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques
    • A61F2002/30952—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques using CAD-CAM techniques or NC-techniques

Definitions

  • the invention relates to improved orthopedic implants and guide tools, including patient-adapted (e.g., patient-specific and/or patient-engineered) designs and procedures, as well as related methods, designs and models.
  • patient-adapted e.g., patient-specific and/or patient-engineered
  • implant components typically employ a one-size-fits-all or few-sizes-fit-all approach to implant design (including modular and assemble able designs) and utilize gross anatomical measurements such as the maximum bone dimensions at the implant site, as well as the patient weight and age, to determine a "suitable" implant. Due to the limited number of sizes and/or shapes of such implant components (previously stockpiled for patient use), these pre-existing implants are typically only able to approximate, but not match, the particular patient's biological features.
  • procedures are designed or otherwise modified to account for and accommodate one or more features of the individual anatomy of the patient undergoing the surgical procedure.
  • Such systems typically utilize non-invasive imaging data, taken of the individual pre-operatively, to guide the design and/or selection of the implant, surgical tools, and the planning of the surgical procedure itself.
  • Various objectives of these newer systems include: (1 ) reducing the amount of bony anatomy removed to accommodate the implant, (2) designing/selecting an implant that replicates and/or improves the function of the natural joint, (3) increasing the durability and functional lifetime of the implant, (4) simplifying the surgical procedure for the surgeon, (5) reducing patient recovery time and/or discomfort, and (6) improving patient outcomes.
  • Various embodiments described herein include advancements relevant to both traditional implants as well as patient-adapted articular implants, allowing such implants to be tailored (to varying degrees) to better address the needs of individual patients as well as various patient groupings. While patient-adapted articular implants offer numerous advantages over traditional one-size-fits-all or few- sizes-fit-all approaches, various embodiments described herein can be used to improve surgical outcomes for all types of implants.
  • patient- adapted articular implants can be selected, designed and/or created from images of the patient's joint and/or other anatomical structures. Based on the images, patient- adapted implant components can be selected and/or designed to include features (e.g., surface contours, curvatures, widths, lengths, thicknesses, and other features) that match existing features in the single, individual patient's joint as well as features that approximate an ideal and/or healthy feature that may not exist in the patient prior to a procedure. Moreover, by altering the design and/or selection approach to address various potential and actual design implant issues, non-traditional design approaches have been identified that offer improvements over traditional implant designs and surgical procedures.
  • features e.g., surface contours, curvatures, widths, lengths, thicknesses, and other features
  • Patient-adapted features can include patient-specific features as well as patient-engineered features.
  • Patient-specific (or patient-matched) implant component or guide tool features can include features adapted, designed, modified and/or manufactured to match or substantially match one or more of the patient's biological features, for example, one or more biological/anatomical structures, alignments, kinematics, and/or soft tissue features.
  • Patient-engineered (or patient-derived) features of an implant component can include features adapted, designed modified and/or manufactured (e.g., preoperatively designed and manufactured) based at least partially on patient-specific data in combination with various other data sources and/or various engineering and design principles to substantially enhance or improve one or more of the patient's anatomical and/or biological features.
  • features of an implant component, guide tool or related surgical method can be achieved by analyzing patient imaging data and designing and/or selecting (e.g., preoperatively selecting from a physical or electronic library of implant components and/or component designs) an implant component, a guide tool, and/or a procedure having a feature that is matched, optimized and/or otherwise modified for a particular patient's biology.
  • Such features can include pre- primary or primary articular implant components having (a) an outer, joint-facing surface, (b) an inner, bone-facing surface, (c) a peripheral edge, and (d) assorted internal physical characteristics of the implant.
  • the outer, joint-facing surface can include a bearing surface or other surfaces, while the inner joint facing surface and/or the peripheral edge can be designed and/or selected to accommodate one or more patient-engineered bone cuts selected and/or designed from patient-specific data.
  • the implant components, tool and surgical procedures can be can be applied to any joint including, without limitation, a spine, spinal articulations, an intervertebral disk, a facet joint, a shoulder, an elbow, a wrist, a hand, a finger, a hip, a knee, an ankle, a foot, or a toe joint.
  • one articular implant component can be a femoral implant component for a knee joint.
  • the implant components can be selected and/or designed to accommodate any number and/or shape of prepared anatomical support surfaces, include accommodating no prepared surfaces (i.e., attaching to the pre-existing surfaces of the patient's articular anatomy).
  • FIGS. 1A and 1 B show schematic representations in a coronal plane of a patient's distal femur (FIG. 1A) and a femoral implant component (FIG. 1 B);
  • FIGS. 2A to 2E show optimized resection cut planes to a patient's femur based on the medial condyle.
  • FIGS. 3A and 3B show resection cut planes for a patient's lateral condyle posterior chamfer (FIG. 3A) and lateral condyle posterior (FIG. 3B) cut planes that are independently optimized based on patient-specific data for the lateral condyle;
  • FIGS. 4A-4C illustrate a femoral implant component having six bones cuts that include one or more parallel and non-coplanar facets
  • FIGS. 5A-5B illustrate a femoral implant component having seven bones cuts that include one or more parallel and non-coplanar facets
  • FIG. 6 illustrates a resection cut facet separated from one or more corresponding facets by an intercondylar space and/or by a step cut
  • FIGS. 7A and 7B are schematic views of a femur and patella and exemplary resection cut planes
  • FIGS. 8A and 8B illustrate a patient-specific femoral model and posterior and anterior resection cut lines for a patient-specific implant component having a curvilinear cut
  • FIG. 9A to FIG 9C illustrate steps for performing a curvilinear resection cut between planar anterior and posterior cuts on a medial condyle
  • FIGS. 10A to 10C illustrate steps for performing a curvilinear resection cut between planar anterior and posterior cuts on a lateral condyle;
  • FIG. 11 shows a guide tool for making distal and posterior resection cuts to the distal femur;
  • FIGS. 12A and 12B show two options for a third guide tool for making anterior and posterior chamfer cuts
  • FIG. 13 illustrates a guide tool having one or more apertures for establishing resected holes in a patient's biological structure
  • FIG. 14 illustrates a guide tool having a moveable aperture and bushing
  • FIG. 15A depicts a set of three medial spacer block inserts having incrementally increasing thicknesses
  • FIGS. 15B depicts a set of two medial femoral trials having incrementally increasing thicknesses
  • FIGS. 15C depicts a medial femoral trial in place and a spacer block being inserted to evaluate the balance of the knee in flexion and extension;
  • FIGS. 16A depicts a set of three medial tibial component insert trials having incrementally increasing thicknesses;
  • FIG. 16B depicts the process of placing and adding various tibial component insert trials;
  • FIG. 16C depicts the process of placing the selected tibial component insert;
  • FIGS. 17A, 17B, and 17C illustrate a set of three guide tools, which collectively supplied all of the guide slots and holes to perform each of several predetermined femoral resection cuts and peg hole placements;
  • FIGS. 18A through 18F illustrate a different set of femoral guide tools to perform each of several predetermined femoral resection cuts and peg hole placements
  • FIG. 19 is a flow chart illustrating an exemplary process for selecting and/or designing a patient-adapted total knee implant
  • FIG. 20 depicts an implant or implant design that includes a straight distal cut, a straight anterior cut, a straight posterior cut, and curvilinear chamfer cuts;
  • FIGS. 21 A through 21 F illustrate exemplary types of curvatures for one or more condylar coronal or sagittal curvatures;
  • FIGS. 22A and 22B illustrate two femoral implant components, one having a J-curve that is substantially patient-specific and one having a J-curve that is partially patient-specific and partially patient-engineered;
  • FIG. 23A illustrates the use of a coronal curvature having a longer radius of curvature versus a coronal curvature having shorter radius of curvature
  • FIG. 23B illustrates an alternate embodiment of the use of a coronal curvature having a longer radius of curvature versus a coronal curvature having shorter radius of curvature
  • FIG. 24 illustrates a patient's J-curve can be determined independently for lateral and medial condyles
  • FIG. 25A shows a five-cut-plane femoral resection design for a femoral implant component having five bone cuts
  • FIG. 25B shows a seven-cut-plane femoral resection design for a femoral implant component having seven bone cuts
  • FIG. 26A shows a patient's femur having five, flexed resection cuts
  • FIG. 26B shows the same femur but with five, not flexed resection cuts
  • FIGS. 27A to 27F illustrate patient-adapted femoral implants and resection cuts for each of the three patients.
  • FIG. 28A and 28B show exemplary unicompartmental medial and lateral tibial implant components without (FIG. 28A) and with (FIG. 28B) a
  • FIGS. 29A to 29C depict three different types of step cuts separating medial and lateral resection cut facets on a patient's proximal tibia;
  • FIG. 30A depicts a patient's native tibial plateau in an uncut condition
  • FIG. 30B depicts one embodiment of an intended position of a metal backed component and insert for treating the tibia of FIG. 30A
  • FIG. 30C depicts an alternate embodiment of an intended position of a metal backed component and insert for treating the tibia of FIG. 30A;
  • FIG. 30D depicts another alternate embodiment of an intended position of a metal backed component and insert for treating the tibia of FIG. 30A;
  • FIGS. 31 A and 31 B show exemplary flow charts for deriving a medial tibial component slope (FIG. 31 A) and/or a lateral tibial component slope (FIG. 31 B) for a tibial implant component;
  • FIG. 32 illustrates a coronal plane of the knee with exemplary resection cuts that can be used to correct lower limb alignment in a knee replacement
  • FIGS. 33A through 33J show exemplary combinations of tibial tray designs
  • FIGS. 34A through 34F include additional embodiments of tibial implant components that are cruciate retaining;
  • FIGS. 35A through 35K show implant components with exemplary features that can be selected and/or designed, e.g., derived from patient-specific and adapted to a particular patient, as well as be included in a library;
  • FIG. 36 depicts a condylar J-curve offset that desirably achieves a similar kinematic motion
  • FIGS. 37A to 37C show exemplary steps for altering a blank tibial tray and a blank tibial insert to each include a patient-adapted profile, for example, to substantially match the profile of the patient's resected tibial surface;
  • FIGS. 38A to 38D show four different exemplary tibial implant profiles, for example, having different medial and lateral condyle perimeter shapes;
  • FIGS. 39A and 39B show bone cement pockets in an embodiment of an implant component (FIG. 39A) and in a traditional component (FIG. 39B);
  • FIGS. 40A through 40K depict various views of one embodiment of a set of alignment jigs and associated tools for guiding a surgeon in performing various femoral cuts in preparation for the implantation of a femoral implant;
  • FIG. 41 depicts one embodiment of a flexion gap balancer block for use in a knee brought into flexion;
  • FIGS. 42A, 42B and 42C depict views of an additional balancing technique to properly align a desired external rotation to the knee prosthesis prior to insertion of a tibial tray and tibial insert;
  • FIGS. 43A-43M illustrate exemplary traditional implants including traditional knee-joint implants (FIGS. 43A and 43B), traditional hip-joint implants (FIGS. 43C-43G), traditional shoulder-joint implants (FIGS. 43H-43J), and traditional spinal implants (FIGS. 43K-43M);
  • FIGS. 44A and 44B illustrate models for one particular patient receiving a single compartment knee implant and in need of osteophyte removal prior to placement of the implant components
  • FIGS. 45A and 45B illustrate models for one particular patient receiving a bicompartmental knee implant and in need of osteophyte removal prior to placement of the implant components
  • FIGS 46A through 46E depict various methods of crosslinking materials using a focused radiation beam and/or x-ray source
  • FIG. 47A depicts a normal humeral head and upper humerus which forms part of a shoulder joint
  • FIG. 47B depicts a humeral head having an alignment jig designed to identify and located various portions of the humeral anatomy
  • FIG. 47C depicts an alternative embodiment of a humeral head jig that utilizes an alternative conforming surface to align the jig;
  • FIG. 48A depicts a humeral head with osteophytes
  • FIGS. 48B and 48C depict the humeral head of FIG. 48A with a more normalized surface that has been corrected by virtual removal of the osteophytes;
  • FIG. 49A depicts a humeral head with voids, fissures or cysts
  • FIGS. 49B and 49C depict the humeral head of FIG. 49A with a more normalized surface that has been corrected by virtual removal of the voids, fissures or cysts;
  • FIG. 1 [00079]
  • FIG. 1 [00081 ]
  • FIG. 50C
  • FIGS. 51 C and 51 D depict two alternative embodiments of a glenoid jig for use with the glenoid of FIG. 51 A, each of which incorporates conforming surfaces that accommodate the osteophytes;
  • FIG. 52A depicts a glenoid component with voids, fissures or cysts
  • FIG. 52B depicts the glenoid component of FIG. 52A with a more normalized surface that has been corrected by virtual "filling" of the voids, fissures or cysts;
  • FIG. 52C depicts an embodiment of a glenoid jig for use with the glenoid component of FIG. 52A, which incorporates various conforming surfaces that accommodate the voids, fissures and/or cysts (and other surfaces) of the glenoid component.
  • a significant advantage conferred by preoperative imaging, anatomical modeling and design/selection of surgical implants, tools and procedural steps is the ability to address, assess, correct, modify and/or accommodate anatomical variation and/or asymmetry as well as a wide variety of other differences and/or disparities in the treated anatomy of an individual patient or patient group.
  • the virtually unlimited number of potential implant sizes and/or shapes that can be designed and/or selected, in combination with the opportunity for a personalized surgical plan, allows a physician to optimize the joint repair in many ways, including (1 ) minimizing unnecessary bone resection, (2) restoring and/or improving joint kinematics and alignment, (3) reducing or minimizing implant wear, fracture and/or fatigue, (4) improving aesthetics of the joint repair, and (5) simplifying the surgical procedure and removing a significant amount of surgical "guesswork.”
  • anatomical data from databases of general and/or specific patent populations (and/or individuals and/or groups therein) can be compared to imaged and/or modeled data, and significant variations in one or more anatomical features (or individual components of such features) can be identified for further study/assessment.
  • database data can be incorporated into various models and utilized to modify and/or optimize one or more features of the surgical implants, tools and procedural steps. Accordingly, surgical implants, tools and procedural steps can be selected and/or designed to incorporate some patient-specific characteristics in combination with non-patient-specific characteristics.
  • an implant or implant system can include one, two, three, four or more components having one or more patient- specific features that substantially match one or more of the patient's biological features, for example, one or more dimensions and/or measurements of an anatomical/biological structure, such as bone, cartilage, tendon, or muscle; a distance or space between two or more aspects of a biological structure and/or between two or more different biological structures; and a biomechanical or kinematic quality or measurement of the patient's biology.
  • an implant component can include one or more features that are engineered to optimize or enhance one or more of the patient's biological features, for example, (1 ) deformity correction and limb alignment (2) preserving bone, cartilage, and/or ligaments, (3) preserving and/or optimizing other features of the patient's anatomy, such as trochlea and trochlear shape, (4) restoring and/or optimizing joint kinematics or biomechanics, and/or (5) restoring and/or optimizing joint-line location and/or joint gap width.
  • an implant component can be designed and/or manufactured to include one or more standard (i.e., non-patient-adapted) features.
  • the patient-adapted implant components and guide tools described herein can include any number of patient-specific features, patient-engineered features, and/or standard features.
  • Illustrative combinations of patient-specific, patient-engineered, and standard features of an implant component are provided in Table 1.
  • Table 1 illustrates an implant or implant component having at least thirteen different features.
  • Each feature can be patient-specific (P), patient- engineered (PE), or standard (St).
  • P patient-specific
  • PE patient- engineered
  • St standard
  • there are at least 105 unique combinations in which each of thirteen is either patient-specific, patient-engineered, or standard features.
  • Table 1 Exemplary combinations of patient-specific (P), patient-engineered (PE), and standard (St) features 1 in an implant
  • S standard, off-the-shelf
  • P patient-specific
  • PE patient-engineered (e.g., constant coronal curvature, derived from the patient's coronal curvatures along articular surface)
  • Each of the thirteen numbered implant features represents a different exemplary implant feature, for example, for a knee implant the thirteen features can include: (1 ) femoral implant component M-L dimension, (2) femoral implant component A-P dimension, (3) femoral implant component bone cut, (4) femoral implant component sagittal curvature, (5) femoral implant component coronal curvature, (6) femoral implant component inter-condylar distance, (7) femoral implant component notch location / geometry, (8) tibial implant component M-L dimension, (9) tibial implant component A-P dimension, (10) tibial implant component insert inter-condylar distance, (1 1 ) tibial implant component insert lock, (12) tibial implant component metal backing lock, and (13) tibial implant component metal backing perimeter.
  • the implants and implant systems described herein can include a combination of implant components, such as a traditional unicompartmental device with a patient-specific bicompartmental device or a combination of a patient-specific unicompartmental device with standard
  • implant combinations allow for a flexible design of an implant or implant system that includes both standard and patient-specific features and components. This flexibility and level of patient-specificity allows for various engineered optimizations, such as retention of alignments, maximization of bone preservation, and/or restoration of normal or near-normal patient kinematics.
  • a single implant component, guide tool, and/or related method can include one or more patient-specific features, one or more patient-engineered features, and/or one or more standard features (e.g., "off-the-shelf).
  • the standard, off-the-shelf features can be selected to best fit with one or more of the patient- specific and/or patient-engineered features.
  • a metal backed tibial component can include a standard locking mechanism and a patient- adapted (i.e., patient-specific or patient-engineered) perimeter of the tibial
  • a patient-specific perimeter of the tibial component can be achieved, for example, by cutting the perimeter of a selected tibial component to match the patient's cortical bone perimeter in one or more dimensions of one more sections.
  • a polyethylene insert can be chosen that includes a standard locking mechanism, while the perimeter is adapted for better support to the patient's tibial bone perimeter or the perimeter of the metal backing.
  • an implant, guide tool, and/or related method can include one or more patient-adapted features and one or more standard features.
  • the joint-facing surface of an implant component can include a patient-specific feature (e.g., curvature) in the axis or axes of motion and one or more standard features in other axes.
  • a patient-specific feature e.g., curvature
  • patient-engineered Using a curvature in the direction of motion that is matched to the patient's curvature (patient-specific) or that is optimized based on the patient's curvature (patient-engineered) can help to maintain and/or improve the biomechanical aspects of the patient's joint.
  • the joint-facing surface of a condylar portion of a femoral implant component and/or a corresponding groove in the bearing surface of a tibial implant component can include a patient-specific sagittal curvature (e.g., having one or more patient-specific radii of curvature) and a standard coronal curvature or radii of curvature.
  • Coronal radii of curvature also can be patient-derived, but an average or an optimum can be derived across the articular surface that is constant along the extent of the articular surface in the coronal plane.
  • the patient- specific sagittal curvature or radii of curvature can be designed from patient-specific data to match an existing feature of the patient's biology or it can be patient- engineered from patient-specific data to improve an existing feature of the patient's biology.
  • an implant component can include some combination of other patient-adapted features.
  • the joint-facing surface can be designed to, at least in part, substantially negatively-match an opposing surface at the joint cavity (e.g., the surface of the patient's biological structure, native or resected, or the surface of an opposing implant component).
  • an opposing surface at the joint cavity e.g., the surface of the patient's biological structure, native or resected, or the surface of an opposing implant component.
  • the joint-facing surface of the implant component can include patient- adapted features such as a patient-specific sagittal curvature and a patient- engineered coronal curvature, or a patient-specific sagittal curvature and a patient- specific coronal curvature.
  • patient-adapted features such as a patient-specific sagittal curvature and a patient- engineered coronal curvature, or a patient-specific sagittal curvature and a patient- specific coronal curvature.
  • These curvatures can be patient-specific in at least a portion or the entire joint-facing surface of the implant.
  • one or more of these curvatures can be patient-adapted in one condyle, but not patient-adapted in the other condyle.
  • the shape (e.g., curvature) of a first condyle can be used, for example, to generate a shape (e.g., curvature) for the second condyle.
  • the joint-facing surface of an implant component can include one or more standard features.
  • the standard shape of the joint-facing surface of the component can reflect, at least in part, the shape of typical healthy subchondral bone or cartilage.
  • the joint-facing surface of an implant component can include a curvature having standard radii or curvature in one or more directions.
  • an implant component can have a standard thickness or a standard minimum thickness in select areas.
  • Standard thickness(es) can be added to one or more sections of the joint-facing surface of the component or, alternatively, a variable thickness can be applied to the implant component.
  • An implant i.e., an implant system
  • an implant system can include one or more patient-adapted (e.g., patient-specific and/or patient-engineered) implant components and one or more standard implant components.
  • a knee implant can include a femoral implant component having one or more patient-adapted and standard features, and an off-the-shelf tibial implant component having only standard features.
  • the entire tibial implant component can be off-the-shelf.
  • a metal-backed implant component (or portion of an implant component) can be patient-specific, e.g., matched in the A-P dimension or the M-L dimension to the patient's tibial cortical bone, while the corresponding plastic insert implant component (or corresponding portion of the implant component) can include a standard off-the-shelf configuration.
  • Off-the-shelf configuration can mean that the tibial insert has fixed, standard dimensions to fit, for example, into a standard tibial tray.
  • Off-the-shelf configuration also can mean that the tibial insert has a fixed, standard dimension or distance between two tibial dishes or curvatures to accommodate the femoral bearing surface.
  • the latter configuration is particularly applicable in an implant system that uses a femoral implant component that is patient-specifically matched in the M-L dimension to the distal femur of the patient's bone, but uses a standardized intercondylar notch width on the femoral component to achieve optimal mating with a corresponding tibial insert.
  • FIG. 1A and 1 B show schematic representations in a coronal plane of a patient's distal femur (FIG. 1 A) and a femoral implant component (FIG. 1 B).
  • the implant component M-L dimension 100 e.g. epicondylar M-L dimension
  • the intercondylar M-L dimension (i.e., notch width) of the implant component, 104 can be standard, which in this figure is shorter than the patient's intercondylar M-L dimension 106.
  • the epicondylar M-L dimension of the implant component is patient-specific, while the intercondylar M-L dimension (i.e., notch width) is designed to be a standard length, for example, so that is can properly engage during joint motion a tibial insert having a standard distance between its dishes or curvatures that engage the condyles of the femoral implant component.
  • the optimized number of cut planes, depths of cut planes, angles of cut planes and/or orientations of cut planes can be determined independently for each of the medial and lateral femoral condyles. This type of independent optimization between condyles can result in a different number of cut plane facets, different angles of cut plane facets, and/or different depths of cut plane facets on corresponding portions of medial and lateral condyles.
  • resection cuts can be planned for a medial and lateral femoral condyle.
  • a single bone cut can be optimized in a patient to maximize bone preservation in that select area, for example, a posterior condyle.
  • multiple or all resection cuts can be optimized.
  • one or more resection cuts can be optimized in the femur individually for each condyle, resulting in resection cuts placed at a different depths, angles, and/or orientations in one condyle relative to the other condyle.
  • a horizontal cut in a medial condyle may be anatomically placed more inferior relative to the limb than a horizontal cut in a lateral condyle.
  • the distance of the horizontal cut from the subchondral bone may be the same in each condyle or it can be different in each condyle.
  • Chamfer cuts in the medial and lateral condyle may be placed in different planes rather than the same plane in order to optimize bone preservation.
  • chamfer cuts in the medial and lateral condyle may be placed at a different angle in order to maximize bone preservation.
  • Posterior cuts may be placed in a different plane, parallel or non- parallel, in a medial and a lateral femoral condyle in order to maximize bone preservation.
  • a medial condyle may include more bone cut facets than a lateral condyle in order to enhance bone preservation or vice versa.
  • a measure of bone preservation can include total volume of bone resected, volume of bone resected from one or more resection cuts, volume of bone resected to fit one or more implant component bone cuts, average thickness of bone resected, average thickness of bone resected from one or more resection cuts, average thickness of bone resected to fit one or more implant component bone cuts, maximum thickness of bone resected, maximum thickness of bone resected from one or more resection cuts, maximum thickness of bone resected to fit one or more implant component bone cuts.
  • FIGS. 2A to 2E show optimized cut planes based on the medial condyle.
  • FIGS. 3A and 3B show cut planes for the lateral condyle posterior chamfer (FIG. 3A) and lateral condyle posterior (FIG. 3B) cut planes that are independently optimized (i.e., relative to the medial condyle posterior chamfer and medial condyle posterior cut planes, respectively) based on patient-specific data for the lateral condyle
  • an implant component bone cut can include one or more non-parallel and non- coplanar facets.
  • the implant component in FIG. 4A includes six bone cuts while the implant component in FIG. 5A includes an extra posterior chamfer bone cut for a total of seven bone cuts.
  • Non-coplanar facets can include facets that lie in parallel but different planes and/or facets that lie in non-parallel planes. As exemplified by the implant component shown in FIGS. 4A-4B and by the implant component shown in FIGS.
  • the medial and lateral facets of a bone cut can be non-parallel and non-coplanar for one or more bone cuts, for example, for one or more of the distal bone cut 4410, the posterior bone cut 4430, the first posterior chamfer bone cut 4452, and the second posterior chamfer bone cut 4454.
  • one or more corresponding facets of a bone cut can include different thicknesses.
  • the implant component shown in FIG. 4A includes a maximum distal medial facet thickness of 6.2 mm and a maximum distal lateral facet thickness of 6.3 mm.
  • the independent and optionally patient-derived thicknesses on corresponding bone cut facets can apply to one or more thickness measurements, for example, one or more of maximum thicknesses, minimum thickness, and an average thickness, for example, to match or optimize the particular patient's anatomy.
  • a single bone cut or bone cut facet can include a variable thickness (e.g., a variable thickness profile across its M-L and/or A-P dimensions.
  • a bone cut or bone cut facet can include a thickness profile in one or more dimensions that is patient-derived (e.g., to match or optimize the patient's anatomy).
  • the implant component in FIG. 5A includes an anterior chamfer with an 1 1 mm thickness on the medial side (which includes the medial implant component peg or post 4465) and a different thickness on the lateral side.
  • the implant component in FIG. 5A was selected and/or designed to have a flex-fit (e.g., having bone cuts rotated posteriorly about the transepicondylar axis, which can enhance implant component coverage of the posterior portion of the femur and provide the patient with deeper knee flexion with the implant.
  • one or more corresponding facets of a bone cut can include different surface areas or volumes.
  • the asymmetric facets appear dissimilar in shape and/or size (e.g., two-dimensional area).
  • the implant components shown in FIGS. 4A and 5A include one or more corresponding facets (e.g., distal medial and lateral facets, posterior medial and lateral facets, and/or posterior chamfer medial and lateral facets) having different medial facet and lateral facet bone-facing surface areas, joint-facing surface areas, and/or volumes in between the two surfaces.
  • the medial and lateral facets of the distal bone cut 4410 are asymmetric and appear dissimilar in both shape (e.g., surface area perimeter shape) and size (e.g., volume under the surface area).
  • the independent facet surface areas and/or volumes optionally can be patient-derived (e.g., to match or optimize the patient's anatomy).
  • non-coplanar facets can be separated by an intercondylar space 4414 and/or by a step cut 4415.
  • the distal bone cut 4410 includes non-coplanar medial and lateral facets that are separated, in part, by the intercondylar space 4414 and, in part, by a step cut 4415.
  • one or more resection cuts can be selected and/or designed to so that one or more resected cut or facet surfaces substantially matches one or more corresponding bone cuts or bone cut facets.
  • FIG. 4C shows six resection cut facets that substantially match the corresponding implant component bone cut facets shown in FIG. 4A.
  • FIG. 5B shows seven resection cut facets that substantially match the corresponding implant component bone cut facets of the medial side of the implant component shown in FIG. 4A.
  • the portion 4470 represents additional bone conserved on the lateral side of the of the femur corresponding to the bone-cut intersection between the lateral distal bone cut facet 4410 and the adjacent anterior chamfer bone cut 4440.
  • a bone-cut facet and/or a resection cut facet can span the intercondylar space and be separated from another facet by a step cut.
  • predetermined resection cuts can be selected and/or designed to include a facet or part of a facet 4680 separated from one or more corresponding facets by an intercondylar space 4614 and/or by a step cut 4615.
  • one or more of the implant bone cuts can be asymmetric, for example, asymmetric with respect to a sagittal or A-P plane, or to a coronal or M-L plane, bisecting the implant component.
  • the anterior chamfer bone cut 4440 is asymmetric with respect to an A-P plane bisecting the implant component.
  • the lateral distal bone cut facet 4410 is asymmetric with respect to an A-P plane bisecting the implant component.
  • asymmetric bone cuts and bone cut facets can be employed on a bone-facing surface of a femoral implant component to save substantial portions of bone.
  • Table 2 shows the different amounts of bone to be resected from a patient for fitting an implant component with bone cuts shown in FIG. 4A, an implant component with bone cuts shown in FIG. 4A, and a traditional implant component with traditional bone cuts.
  • the implant component shown in FIG. 4A saves 44% of resected patient bone and the implant component shown in FIG. 5A saves 38% of resected patient bone.
  • the implant component in FIG. 5A is flexed, which can provide enhanced deep knee flexion for the patient.
  • the surgeon or operator can select or apply a weighting to these two parameters (bone preservation and kinematics) and optionally other parameters to identify an optimum patient-adapted implant component and, optionally, a corresponding resection cut strategy that meets the desired parameters and/or parameter weightings for the particular patient.
  • the anterior or trochlear bone cut is located substantially in the coronal plane and is parallel to the posterior condylar bone cut, as indicated by the dashed anterior resection cut 4710 and dashed posterior resection cut 4712 shown in FIG. 7A. This can result in a
  • the implant's anterior or trochlear bone cut is substantially non-parallel to the coronal plane, as shown by the dashed and straight line 4718 in FIG. 7B.
  • the implant's anterior or trochlear bone cut can substantially match the patient's resected trochlear surface, which can be selected and/or designed to be parallel to a tangent through the corresponding peak 4720 and an uncut trochlear surface portion of the patient's trochlea, as shown in FIG. 7B.
  • implant bone cut 4718 and the resected surface By placing the implant bone cut 4718 and the resected surface at an angle relative to the patient's coronal plane, for example, parallel to a tangent of one or both medial and lateral trochlear peak and/or the adjacent trochlear surface, a substantial amount of bone can be preserved.
  • the implant component can include a trochlear bone cut with two or more non-coplanar facets, as shown by the intersecting solid lines 4722, 4724 in FIG. 7B.
  • one of the two or more facets (and the patient's corresponding resected surface) can be substantially parallel to the patient's lateral uncut trochlear peak 4720 and/or the adjacent uncut trochlear surface.
  • a second facet (and the patient's corresponding resected surface) can be substantially parallel to the patient's medial uncut trochlear peak 4726 and/or the adjacent uncut trochlear surface. This can further enhance the degree of bone preservation.
  • two or more trochlear bone cut facets can be substantially tangent to the lateral and medial patellar surfaces 4728, 4730 of the patient's uncut bone.
  • two or more trochlear bone cuts can be substantially tangent or parallel to the superior and inferior patellar facets, in particular, when more than two implant trochlear bone cut facets are used.
  • one or more trochlear bone cut facets can be curvilinear.
  • the posterior bone cut includes portions on the medial and lateral condyles that are in the same plane and parallel to each other, and substantially parallel to the anterior cut.
  • the implant component can include posterior condylar bone cut facets on the medial and lateral condyles, respectively, that are non-coplanar 4732, 4734.
  • the implant component can include one or more posterior condylar facets that are substantially non-parallel with one or more facts of the anterior bone cut.
  • the posterior bone cut medial and lateral facets of an implant component can be asymmetric with respect to an A-P plane bisecting the implant component.
  • one or more posterior bone cut facets can be curvilinear.
  • the distal bone cut of a femoral implant component includes medial and lateral condylar facets that are in the same plane as each other and/or are substantially parallel to each other.
  • the facets can be separated by the intercondylar space and/or by a step cut.
  • the implant component can include a distal bone cut having medial and lateral condylar facets that are non-coplanar and/or non-parallel.
  • the distal bone cut or bone cut facets is/are asymmetric with respect to an A-P plane bisecting the implant component. Moreover, the distal bone cut and/or one or more distal bone cut facets can be curvilinear.
  • the implant component can include a posterior chamfer bone cut that includes medial and lateral condylar facets that are non- coplanar and/or non-parallel.
  • a posterior chamfer bone cut of the implant component can include facets that are asymmetric with respect to an A-P plane bisecting the implant component.
  • one or more posterior chamfer bone cuts and/or one or more posterior chamfer bone cut facets can be curvilinear.
  • the implant component can include an anterior chamfer bone cut that includes medial and lateral condylar facets that are non- coplanar and/or non-parallel.
  • an anterior chamfer bone cut of the implant component can be asymmetric and/or can include facets that are asymmetric with respect to an anterior-posterior (A-P) plane bisecting the implant component.
  • A-P anterior-posterior
  • one or more anterior chamfer bone cuts and/or bone cut facets can be curvilinear.
  • an implant component and associated surgical plan can be designed to incorporate both straight and curvilinear bone cuts on its bone-facing surface.
  • a femoral implant can be designed to include 3 mm curvilinear cut depths and corresponding implant thicknesses along the distal portion of each condyle. The cut depth and implant thickness along each condyle can be designed independently of the other condyle.
  • jigs for performing the curvilinear cuts to the articular bone surface can be designed and/or selected.
  • FIGS. 8A and 8B posterior and anterior resection cut lines are created in the model, as shown in FIGS. 8A and 8B.
  • a medial split line is identified on the condyle, as shown in FIG. 9A, and then a 3 mm deep cut line is generated to follow the split line, as shown in FIG. 9B.
  • the resulting virtual curvilinear cut is shown in FIG 9C.
  • the same steps are performed independently for the lateral condyle, as shown in FIGS. 10A to 120C.
  • the guide tools can include one or more surfaces and/or structures that are designed and/or selected using patient-specific anatomical data.
  • the guide tool surface(s) that conform to or mirror existing anatomical structures (and/or anatomical structures modified during the surgical procedure) can be placed adjacent to specific anatomical structures in a desired position and/or orientation, and provide guiding surfaces and/or other features that assist a surgeon in creating a desired resection plane, drill hole, etc., as described herein.
  • Resection cut guide tools can be designed to be patient-specific on their bone-facing surface to allow a snap-fit onto a particular patient's femur.
  • other features such as thickness, joint-facing surface, and peg placement and size, also can be patient-specific or patient-engineered.
  • one or more features can be standard.
  • a cut guide tool can be designed to rest on 2 mm thick cartilage relative to CT data and can include a standard tool thickness of 4 mm; however other standard thicknesses can be used, for example, a 2 mm or a 3 mm thickness.
  • the cut guide tool shown in FIG. 11 can include three optional pin placements for stabilization and a posterior beam to give stability and rigidity to the tool.
  • the lateral spacer shown on the left side of FIG. 11 can rest on cut tibia to approximate the thickness of asymmetry.
  • cut guide tools can be designed to follow the cut tool shown in FIG. 11 and can complete the remaining chamfer cuts for the distal femur.
  • Each of the cut tools shown in the figure includes two pin placements for stabilization.
  • the tool on the left includes short pegs to be positioned in the peg holes established by a peg hole driver guide tool, for example, as shown in FIGS. 13 and 14.
  • the tool on the right includes no lateral peg to allow for external rotation of the guide tool to establish rotated chamfer cuts.
  • a medial femoral trial and a spacer block can be inserted to evaluate the balance of the knee in flexion and extension.
  • Spacer blocks having different thicknesses can be inserted and evaluated until an optimized thickness is identified.
  • a lateral femoral trial also can be placed between the lateral portions of the femur and tibia and a lateral spacer block inserted and evaluated along with the medial spacer block.
  • Medial and lateral spacer blocks having different thicknesses can be placed and removed until a desired tension is observed medially and laterally throughout the patient's range of motion.
  • a tibial implant component and/or tibial implant component insert can be selected to have a thickness based on the thickness identified by evaluation using the femoral trial and spacer block.
  • the selected medial tibial implant component (and/or tibial implant component insert) and the lateral tibial implant component (and/or tibial implant component insert) can have different thicknesses.
  • FIG. 16A depicts a set of three medial tibial component insert trials having incrementally increasing thicknesses, for example, thicknesses that increase by 0.5 mm, by 1 mm, by 1 .5 mm, or by 2 mm.
  • a corresponding set of lateral tibial component insert trials (having a range of thicknesses) can be used in conjunction with the set of medial tibial component insert trials.
  • a tibial component insert trial can be used, for example, to determine the best insert thickness and/or features of a tibial component insert during the final implantation steps.
  • FIG. 16B depicts the process of placing and adding various tibial component insert trials
  • FIG. 16C depicts the process of placing the selected tibial component insert.
  • FIGS. 17A, 17B, and 17C illustrate the set of three guide tools, which collectively supply all of the guide slots and holes to perform each of the predetermined femoral resection cuts and peg hole placements.
  • This set of guide tools included one or more patient-adapted features.
  • the first guide tool 10780 in the set provides guide holes 10782 for drilling into the patient's femur predetermined holes for receiving the femoral implant component pegs.
  • the guide tool 10780 is attached to the patient's femoral bone 10784.
  • the bone-facing surface of the first guide tool is designed to snap-fit to 3 mm of cartilage on the patient's distal femur.
  • a second balancing chip guide tool 10786 provides distal facet resection guide slots 10788, a slot to mark the termination of the distal lateral resection 10790 (which can be used to establish the step cut between the distal lateral and medial resection facets), and a guide surface 10792 for making the posterior resection cut.
  • This tool 10786 can be used for balancing and assessing implant fit (e.g., based on the fit of the guide tool between the femur and cut tibia in knee extension).
  • a third chamfer cutting guide tool 10794 provided guide slots for the remaining predetermined resection cuts. As shown, the cutting guide slots were identified with numbers 1 -6 to identify the order for performing the resection cuts.
  • a set of femoral guide tools was designed and included to perform predetermined femoral resection cuts and peg hole placements, as shown in FIGS. 18A through 18F.
  • a femoral trial guide tool 10830 was designed and included to guide the hole placement for the pegs on the subsequently used guide tools and on the femoral implant component.
  • this guide tool 10830 includes marks incorporated into its joint-facing surface to indicate to the surgeon the locations representing the Whiteside Line 10832 and Epicondylar Axis 10834. As shown in FIG.
  • the second guide tool a balancer chip guide tool 10836
  • a balancer chip guide tool 10836 was designed and included for guiding independent distal medial 10838 and distal lateral 10840 facet cuts, as well as the step cut 10842.
  • Both the femoral trial guide tool 10830 and the balancer chip guide tool 10836 included a bone-facing surface derived from patient-specific data and designed to rest on 3 mm of cartilage atop the patient's femoral bone surface.
  • the balancer chip guide tool 10836 was provided in six different thicknesses to allow the surgeon to use the tool 10836 for ligament balancing and assessment of the implant fit (e.g., by observing the space or tightness of the tool 1636 positioned between the femur and cut tibia during flexion and extension).
  • a spacing paddle tool 10844 as shown in FIG. 18C, was designed and included for representing the extra asymmetric lateral poly thickness when balancing.
  • a chamfer cut guide tool 10846 was designed and included for guiding an anterior resection cut 10848, an anterior chamfer resection cut 10850, and independent posterior medial 10852 and posterior lateral 10854 facet cuts.
  • the a chamfer cut guide tool 10846 was designed with pegs to fit into the previously prepared peg holes in the patient's femur and with each cutting slot numbered for the order in which the cuts were to be performed.
  • a pair of angled cut guides 10856, 10858 was designed and included to facilitate the first and second posterior chamfer cuts.
  • each angled cut guide 10856, 10858 includes a first surface that matches the distal resection surface and, optionally, includes pegs to fit into the previously prepared peg holes in the patient's femur.
  • the distal resection surface includes two non-co-planar facets, which first cut guide surface matches.
  • each angled cut guide 10856, 10858 also includes a second cutting guide surface angled at the predetermined angle of the corresponding chamfer cut such that a cutting tool placed against the surface cuts into the patient's bone at the
  • patient-specific measurements selected for evaluation can be used to select (e.g., from a library), to design, and/or to select and design an implant component having one or more measurements corresponding to or derived from the one or more of the assessed and/or derived patient-specific measurements.
  • the implant component can include one or more patient-specific measurements and/or one or more patient-engineered
  • one or more patient-specific models, one or more patient- adapted surgical steps, and/or one or more patient-adapted surgical guide tools also can be selected and/or designed to include one or more measurements
  • the design and/or selection of implant components, tools and surgical plans for a specific patient, as described herein, can include a wide variety of considerations, options and balancing of competing objectives. In many cases, it may not be absolutely necessary to design and/or select a completely personalized implant and surgical plan, but rather the final implant design can comprise a blending or "composite" of varying aspects of patient-specific, patient-engineered and/or standard features. Such blending can encompass the use of various combinations of such features to create a single implant feature, such as the blending of a patient- specific condylar curvature with a standard condylar curvature to create a single condylar feature on the implant. As disclosed herein, the features of one aspect of the implant need not be symmetrical and/or identical to other aspects of the implant (i.e., the medial and lateral sides of an implant may be dissimilar and/or asymmetric in various ways).
  • FIG. 19 shows one exemplary process for planning the repair and/or replacement of patient anatomy. These steps can be performed virtually, for example, by using one or more computers that have or can receive patient-specific data and specifically configured software or instructions to perform such steps.
  • image data/models can be acquired and limb alignment and deformity corrections are determined, to the extent that either is needed for a specific patient's situation.
  • step (2) the requisite tibial and femoral dimensions of the implant components are determined based, at least in part, on patient-specific data obtained, for example, from image data of the patient's knee.
  • a resection cut strategy can be planned to accommodate user-defined parameters, such using asymmetric cuts and/or implant designs that correct a patient's misalignment and/or maximize bone preservation.
  • the surgical plan can maximize bone preservation by virtually determining a resection cut strategy for the patient's femur and/or tibia that provides minimal bone loss optionally while also meeting other user-defined parameters such as, for example, maintaining a minimum implant thickness, using certain resection cuts to help correct the patient's misalignment, removing diseased or undesired portions of the patient's bone or anatomy, and/or other parameters.
  • This general step can include one or more of the steps of (i) simulating resection cuts on one or both articular sides (e.g., on the femur and/or tibia), (ii) applying optimized cuts across one or both articular sides, (iii) allowing for non-co-planar and/or non- parallel femoral resection cuts (e.g., on medial and lateral corresponding portions of the femur) and, optionally, non-co-planar and/or non-parallel tibial resection cuts (e.g., on medial and lateral corresponding portions of the tibia), and (iv) maintaining and/or determining minimal material thickness.
  • the minimal material thickness for the implant selection and/or design can be an established threshold, for example, as previously determined by a finite element analysis ("FEA") of the implant's standard characteristics and features.
  • FEA finite element analysis
  • the minimal material thickness can be determined for the specific implant, for example, as determined by an FEA of the implant's standard and patient-specific characteristics and features.
  • FEA and/or other load-bearing/modeling analysis may be used to further optimize or otherwise modify the individual implant design, such as where the implant is under or over-engineered than required to accommodate the patient's biomechanical needs, or is otherwise undesirable in one or more aspects relative to such analysis.
  • the implant design may be further modified and/or redesigned to more accurately accommodate the patient's needs, which may have the side effect of increasing/reducing implant characteristics (i.e., size, shape or thickness) or otherwise modifying one or more of the various design "constraints" or limitations currently accommodated by the present design features of the implant.
  • this step can also assist in identifying for a surgeon the bone resection design to perform in the surgical theater and it also identifies the design of the bone-facing surface(s) of the implant components, which substantially negatively-match the patient's resected bone surfaces, at least in part.
  • step (4) a corrected, normal and/or optimized articular geometry on the femur and tibia can be recreated virtually.
  • this general step can include, for example, the step of: (i) selecting a standard sagittal profile, or selecting and/or designing a patient-engineered or patient-specific sagittal profile; and (ii) selecting a standard coronal profile, or selecting and/or designing a patient-specific or patient-engineered coronal profile.
  • the sagittal and/or coronal profiles of one or more corresponding medial and lateral portions can include different curvatures.
  • this general step includes one or both of the steps of: (iii) selecting a standard anterior- posterior slope, and/or selecting and/or designing a patient-specific or patient- engineered anterior-posterior slope, either of which optionally can vary from medial to lateral sides; and (iv) selecting a standard poly-articular surface, or selecting and/or designing a patient-specific or patient-engineered poly-articular surface.
  • the patient- specific poly-articular surface can be selected and/or designed, for example, to simulate the normal or optimized three-dimensional geometry of the patient's tibial articular surface.
  • the patient-engineered poly-articular surface can be selected and/or designed, for example, to optimize kinematics with the bearing surfaces of the femoral implant component. This step can be used to define the bearing portion of the outer, joint-facing surfaces (i.e., articular surfaces) of the implant components.
  • a virtual implant model (for example, generated and displayed using a computer specifically configured with software and/or instructions to assess and display such models) can be assessed and can be altered to achieve normal or optimized kinematics for the patient.
  • the outer joint-facing or articular surface(s) of one or more implant components can be assessed and adapted to improve kinematics for the patient.
  • This general step can include one or more of the steps of: (i) virtually simulating biomotion of the model, (ii) adapting the implant design to achieve normal or optimized kinematics for the patient, and (iii) adapting the implant design to avoid potential impingement.
  • the implant selection and/or design which can include manufacturing or machining the implant to the selected and/or designed specifications using known techniques, can include one or more patient-engineered bone-facing surfaces that may negatively-match the patient's resected bone surface.
  • the implant also can include other features that are patient-adapted, such as minimal implant thickness, articular geometry, and kinematic design features. This process can be applied to various joint implants and to various types of joint implants.
  • this design process can be applied to a total knee, cruciate retaining, posterior stabilized, and/or ACL/PCL retaining knee implants, bicompartmental knee implants, unicompartmental knee implants, and other joint implants, for example, for the shoulder, hip, elbow, spine, or other joints.
  • the thickness of an acetabular cup, either metal backing or polyethylene or ceramic or other insert can be adapted based on the patient's geometry, e.g. depth of the actebular fossa, AP, ML, SI dimensions or other parameters including femoral parameters.
  • a selection and/or design process can incorporate any number of target parameters such that any number of implant component features and resection cuts can be selected and/or designed to meet one or more parameters that are predetermined to have clinical value.
  • a selection and/or design process can include target parameters to restore a patient's native, normal kinematics, or to provide optimized kinematics.
  • the process for selecting and/or designing an implant and/or resection cuts can include target parameters such as reducing or eliminating the patient's mid-flexion instability, reducing or eliminating "tight" closure, improving or extending flexion, improving or restoring cosmetic appearance, and/or creating or improving normal or expected sensations in the patient's knee.
  • the design for a tibial implant can provide an engineered surface that replicates the patient's normal anatomy yet also allows for low contact stress on the tibia.
  • the optimization of resection cuts and implant component bone cuts can result in a cut design that has any number of cut planes or facets, depths of cut planes or facets, angles of cut planes or facets, and/or orientations of cut planes or facets.
  • various other parameters can be included in the cut plane optimization. For example, a flexed cut design can be used to help preserve, restore, or enhance the patient's joint kinematics.
  • Additional parameters that may be included in the determination of optimized resection and bone cuts can include, but are not limited to, one or more of: (1 ) deformity correction and/or limb alignment (2) maximizing preservation of cartilage, or ligaments, (3) maximizing preservation and/or optimization of other features of the patient's anatomy, such as trochlea and trochlear shape, (4) further restoration and/or optimization of joint kinematics or biomechanics (5) restoration or optimization of joint-line location and/or joint gap width, and (6) preservation, restoration, or enhancement of other target features.
  • Various of the described embodiments will be best suited for treating non-uniform or tilted natural anatomy and/or resections of partial or total knees, while others will be more appropriate for the treatment of non-uniform or tilted natural anatomy and/or resections of other joints, including a spine, spinal articulations, an intervertebral disk, a facet joint, a shoulder, an elbow, a wrist, a hand, a finger, a hip, an ankle, a foot, or a toe joint.
  • Certain embodiments described herein include a femoral implant component having one or more patient-adapted (e.g., patient-specific or patient- engineered) features and, optionally, one or more standard features.
  • Various embodiments herein are directed to implants or implant designs optimized to achieve minimal implant thickness, which can include the incorporation of a higher number of bone cuts, for example, six, seven, eight, nine or more bone cuts, on the inner, bone- facing surface of the implant.
  • the bone cuts can be oriented in various dimensions, for example, in a flexed-orientation.
  • certain embodiments can include on the inner, bone-facing surface any combination of straight cuts and curvilinear cuts.
  • One or more curvilinear cuts can be designed to substantially positively-match the patient's uncut articular surface, such as a subchondral bone surface exposed by resurfacing.
  • one or more curvilinear cuts can be designed to
  • a cut surface of the patient's bone for example, a cut curvilinear surface.
  • an implant 2400 can include a planar distal cut 2410, a straight anterior cut 2420, a straight posterior cut 2430, and curvilinear chamfer cuts 2440 in between to substantially negatively-match corresponding resected surface(s) of the femur 2450.
  • embodiments described herein can include implants or implant designs that include on the inner, bone-facing surface one or no straight cuts and portions that
  • both medial and lateral condyles include the same minimum implant thickness.
  • the one or more patient-adapted dimensions or features of one or both condyles can include, for example, width in one or more locations, height in one or more locations, intercondylar distance in one or more locations, and one or more curvatures of at least a portion of the joint-facing surface of the condyle.
  • the curvatures can include, for example, one or more of a sagittal curvature on the medial condyle, a coronal curvature on the lateral condyle, a sagittal curvature on the lateral condyle and a coronal curvature on the lateral condyle.
  • the dimensions or features on the medial and lateral condyles of the implant component can be designed and/or selected independently of the corresponding dimensions on the other condyle, provided that patient-specific data (e.g., image data) is available for the appropriate condyle.
  • patient-specific data e.g., image data
  • one or more of the condylar width, area, and height of an implant component can be designed and/or selected preoperatively to be patient-adapted in one or more locations along one or both condyles.
  • curvatures can be selected on the medial condyle and the lateral condyle of an implant component.
  • one or more curvatures of one condyle can be patient-specific, in whole or in part, while one or more curvatures on the same condyle or on the other condyle can be patient-engineered, in whole or in part, or standard, in whole or in part.
  • the one or more patient-adapted (i.e., patient-specific or patient- engineered) curvatures and standard curvatures on the joint-facing surface of a femoral implant component can be combined in a condyle to take on any overall shape.
  • FIGS. 21 A through 21 F illustrate exemplary types of curvatures 3300, 3310, 3320, 3330, 3340 for one or more condylar coronal or sagittal curvatures.
  • An implant component condyle can include a surface curvature corresponding to a section of any one or more geometric shapes, such as a circle, a parabola, a hyperbola, an ellipsoid, and any other geometric shape, optionally standard or patient-adapted or patient-derived.
  • the curvature also can include, in part, a substantially straight line portion, as illustrated by the curvature 3350 in FIG. 21 F.
  • Different portions of a condyle such as the anterior portion, the distal portion, the posterior portion, the load-bearing portion, and/or the non-load-bearing portion, each can include a different curvature than one or more other portions, in a sagittal plane or in a coronal plane or in an axial plane in a trochlea, for example.
  • the load bearing-portion of the medial condyle can include a different curvature than the non-load-bearing portions of the same condyle, and either or both of which can optionally, be different than any or all sections of the lateral condyle.
  • the load bearing-portion of the lateral condyle can include a different curvature than the non-load-bearing portions of the same condyle, and either or both of which can optionally, be different than any or all sections of the medial condyle.
  • FIGS. 22A and 22B illustrate two femoral implant components, one having a J-curve that is substantially patient-specific and one having a J-curve that is partially patient-specific and partially patient-engineered.
  • both implant components shown on the right side of the figure were designed based on patient- specific data.
  • the top implant component includes a J-curve that, at least in its load-bearing portion, substantially positively-matches the patient's J-curve.
  • the bottom implant component includes a J-curve that was engineered in region 3510 to diverge from the patient-specific J-curve.
  • engineered alterations from a patient's existing J-curve can be employed for example, to match or approximate the height of the patient's existing or missing cartilage, to correct an abnormality in the patient's existing J-curve (e.g., arthritic flattening of the condyle, subchondral cysts, or osteophyte formation), to match one or more features of a corresponding implant component (e.g., a tibial implant component), and/or to optimize the patient's biomechanics or one or more other parameters determined by a clinician or operator to be important.
  • an abnormality in the patient's existing J-curve e.g., arthritic flattening of the condyle, subchondral cysts, or osteophyte formation
  • a corresponding implant component e.g., a tibial implant component
  • the femoral implant component is preoperatively designed and/or selected to include one or both condylar, bearing surfaces having a sagittal curvature (e.g., a J-curve) that, at least in part, substantially positively-matches or is derived from the corresponding sagittal curvature of the patient's condyle, e.g. portions of cartilage or subchondral bone or combinations thereof, as determined from patient-specific data including, for example, image data.
  • a sagittal curvature e.g., a J-curve
  • the coronal curvature of the implant component can include a standard curvature, for example, selected by choosing from among a family of 5, 6, 7, 8, 9, or 10 implants or implant blanks the one that includes a coronal curvature that is most similar to the patient's coronal curvature in one or more locations on the curvature.
  • an implant component condyle curvature can be selected by choosing from among a family of implants or implant blanks the one that, as compared to the patient's curvature, includes longer and/or shorter radii of curvature at a load-bearing portion of the curvature, in order to achieve a less constraining or a more constraining biomechanical situation during knee motion.
  • FIG. 23A illustrates the use of a coronal curvature having a longer radius of curvature versus a coronal curvature having shorter radius of curvature.
  • the radii of curvature of a human femoral condyle coronal curvature typically range from 20 to 30 mm.
  • one or both femoral implant component condyles and/or the corresponding curvature of the bearing surface on the tibial implant component include a coronal curvature that matches a particular patient's coronal curvature.
  • one or both femoral implant component condyles and/or the corresponding curvature of the bearing surface on the tibial implant component include a standard coronal curvature within the range of typical human coronal curvatures, for example, from about 20 mm to about 30 mm.
  • one or both femoral implant component condyles and/or the corresponding curvature of the bearing surface on the tibial implant component include a standard coronal curvature outside of the range of typical human coronal curvatures, for example, less than 20 mm, about 15 mm, less than 15 mm, greater than 30 mm, 35 mm, greater than 35 mm, between about 30 mm and about 40 mm, 40 mm, and/or greater than 40 mm.
  • the tibial implant component can be designed to match or reflect at least one of a sagittal femoral curvature or a coronal femoral curvature.
  • the corresponding radii on the tibial implant component can be applied or derived from the femur in a ratio, e.g., 1 :1 , 1 :2, 1 :3, 1 :4, 1 :5, 1 :8, 1 :10, 1 :15, 1 :20, in at least one of a sagittal dimension or a coronal dimension, or combinations thereof, medially only, laterally only, or both.
  • At least a portion of the femoral implant's coronal curvature (e.g., the center portion of the condyle) and/or the corresponding portion of the tibial implant component curvature can correspond to a section of a circle having a radius of curvature less than 20 mm, less than 15 mm, 15 mm, greater than 30 mm, 35 mm, greater than 35 mm, 40 mm, and/or greater than 40 mm.
  • the sagittal and/or coronal curvatures of a patient's condyle can be determined from image data by assessing the surface of the condyle in a
  • the curvature(s) also can be assessed in an axial plane, for example for a patella, a trochlea, a glenoid, or an acetabulum.
  • a patient's J-curve can be determined independently for lateral and medial condyles.
  • one or both of the patient's lateral and medial condylar J-curves can be applied to one or more sections of a femoral implant component's medial and/or lateral J-curves.
  • the distal point of the lateral condyle through a range of motion 3810 and the distal point of the medial condyle through a range of motion 3820 can be assessed in an axial plane, for example for a patella, a trochlea, a glenoid, or an acetabulum.
  • a patient's J-curve can be determined independently for lateral and medial condyles.
  • a model of a patient's femur can be generated from images of the patient's femur.
  • the images can include, for example, x-ray, cone beam CT, digital tomosynthesis, ultrasound, laser imaging, MRI, CT, PET, SPECT, and/or other images and combinations thereof.
  • the patient's J-curve can be transferred onto a single plane (e.g., a substantially sagittal plane) and then that planar curvature, or a portion thereof, can be transferred into the design of the femoral implant component as a single planar curvature.
  • the patient's J-curve can lie in more than one plane and more than one plane can be used to transfer and apply the J-curve to the implant component, for example, such that the J-curve lies in one plane for a portion and then angles away from that plane for a portion.
  • the implant component for example, such that the J-curve lies in one plane for a portion and then angles away from that plane for a portion.
  • one or both of the implant component's condylar J-curves or portions thereof can match the patient's J-curve planar orientation.
  • the implant component's condylar J-curves or portions thereof can match the patient's J-curve planar orientation.
  • corresponding medial and lateral planes that include portions of the patient's medial and lateral J-curves, respectively, can be non-parallel to each other (e.g., angled toward each other anteriorly) or otherwise angled relative to an anatomical feature (e.g., the epicondylar axis, femoral mechanical axis, trochlear J-curve, and/or some other feature).
  • the corresponding J-curve portions of the femoral implant component and, optionally, the tibial implant component can be designed to match this planar orientation.
  • the J-curve or portions thereof e.g., the distal and/or posterior load-bearing portions
  • the medial or lateral femoral condyle can have a constant coronal curvature, which can be standard or patient-derived or selected.
  • the constant coronal curvature can be the same on the medial and the lateral condyle or it can be different.
  • the constant coronal curvature can be combined with a patient- specific or patient -derived, at least in part, sagittal curvature on one or both condyles.
  • FIG. 25A a five-cut-plane femoral resection design for a femoral implant component having five bone cuts can be utilized.
  • FIG. 25B shows an alternative seven-cut-plane femoral resection design for a femoral implant component having seven bone cuts.
  • Each cut design can be performed on the same patient femur (i.e., having identical bone volumes).
  • the corresponding five-bone-cut implant component and seven-bone-cut implant component can be designed to meet or exceed the same minimum implant thickness.
  • the model of the patient's femur having five resection cuts retained bone volume of 103,034 mm 3
  • the model of the patient's femur having seven bone cuts retained a bone volume of 104,220 mm 3 .
  • the seven-bone-cut implant component saved substantially more of the patient's bone stock, in this case more than 1 ,000 mm 3 , as compared to the five-bone cut implant component.
  • FIG. 26B shows a patient's femur having five, not flexed resection cuts
  • FIG. 26A shows the same femur but with five, flexed resection cuts.
  • the model having five, not flexed resection cuts retains a bone volume of 109,472 mm 3
  • the model having five, flexed resection cuts retains a bone volume of 105,760 mm 3 .
  • the not-flexed- five-bone-cut implant component saved substantially more of the patient's bone stock, in this case nearly 4,000 mm 3 , as compared to the flexed-five-bone-cut cut implant component.
  • the flexed cut design can offer other advantages, such as greater posterior coverage and enhanced deep-knee flexion, which can be weighed relative to all selected parameters and accordingly integrated in the selection and/or design of an implant component.
  • the component designs described in this example can save patient bone stock as compared to a traditional implant component and thereby allow the implant to be pre-primary.
  • the implant components may include cut planes (i.e., of resection cuts and bone cuts) that are optimized based on patient-specific data to meet one or more user-defined parameters, as described above.
  • cut planes can be symmetric or asymmetric, parallel or non-parallel, aligned perpendicular to the sagittal plane or not perpendicular, varied from medial to lateral condyle, and/or can include other orientations.
  • the cut plane designs may include a "flexed" (i.e., rotated or offset relative to the biomechanical or anatomical axes) orientation.
  • the design of attachment pegs may also be flexed relative to the biomechanical or anatomical axes.
  • patient-adapted femoral implant components can include six bone cuts.
  • the bone cut design can be designed in conjunction with corresponding resection cuts.
  • FIGS. 27 and 27B, FIGS. 27C and 27D, and FIGS. 27E and 27F show the patient-adapted femoral implant and resection cuts, respectively, for each of the three patients. As exemplified in FIG.
  • the six bone cuts included an anterior bone cut 10310, medial 10320M and lateral 10320L facets of a distal bone cut, medial 10330M and lateral 10330L facets of a posterior bone cut, an anterior chamfer bone cut 10340, medial 10350M and lateral 10350L facets of a first posterior chamfer bone cut, and medial 10360M and lateral 10360L facets of a second posterior chamfer bone cut.
  • the femoral implant component 10305 included a stepped (or "step") cut 10320 between the medial facet 10320M and lateral facet 10320L of the distal bone cut in order to provide enhanced preservation of distal medial bone stock.
  • FIG. 27C relating to the second patient and FIG.
  • FIGS 27E relating to the third patient include similar features as those numbered in FIGS 27A.
  • the non-coplanar distal bone cut facets which can be connected by a stepped cut, allow for independent and optionally minimum resection depths on the medial and lateral portions of an otherwise continuous bone cut (e.g., anterior bone cut, anterior chamfer bone cut, or distal bone cut).
  • the implant component bone cuts for each patient was engineered to specifically-match the resection cuts for the patient (e.g., in cut and/or facet surface areas, angles, relative orientations, and/or other features).
  • the resection cuts included an anterior resection cut 10310', medial 10320M' and lateral 10320L' facets of a distal resection cut, medial 110330M' and lateral 10330L' facets of a posterior resection cut, an anterior chamfer resection cut 10340', medial
  • the femoral implant component included a stepped (or "step") resection cut 10370' between the medial facet 10320M' and lateral facet 10320L' of the distal resection cut.
  • FIG. 27D relating to the second patient and FIG. 27F relating to the third patient include similar features as those numbered in FIGS 27B.
  • the stepped cut 10320' saves substantial bone stock, for example, at the distal medial facet 10320M' in comparison to a distal medial facet cut having the same depth as the distal lateral facet cut.
  • Certain embodiments described herein can include a tibial implant component having one or more patient-adapted (e.g., patient-specific or patient- engineered) features and, optionally, one or more standard features.
  • the one or more patient-adapted features can be designed and/or selected to fit the patient's resected tibial surface.
  • a patient's lateral and/or medial tibial plateaus may be resected independently and/or at different depths, for example, so that the resected surface of the lateral plateau is higher (e.g., 1 mm, greater than 1 mm, 2 mm, and/or greater than 2 mm higher) or lower (e.g., 1 mm, greater than 1 mm, 2 mm, and/or greater than 2 mm lower) than the resected surface of the medial tibial plateau.
  • tibial implant components can be independently designed and/or selected for each of the lateral and/or medial tibial plateaus.
  • the perimeter of a lateral tibial implant component and the perimeter of a medial tibial implant component can be independently designed and/or selected to substantially match the perimeter of the resection surfaces for each of the lateral and medial tibial plateaus.
  • FIG. 28A and 28B show exemplary
  • unicompartmental medial and lateral tibial implant components without (FIG. 28A) and with (FIG. 28B) a polyethylene layer or insert.
  • the lateral tibial implant component and the medial tibial implant component have different perimeters shapes, each of which substantially matches the perimeter of the corresponding resection surface (see arrows).
  • the polyethylene layers or inserts 6010 for the lateral tibial implant component and the medial tibial implant component have perimeter shapes that correspond to the respective implant component perimeter shapes.
  • one or both of the implant components can be made entirely of a plastic or polyethylene (rather than having a having a polyethylene layer or insert) and each entire implant component can include a perimeter shape that substantially matches the perimeter of the corresponding resection surface.
  • the height of a lateral tibial implant component and the height of a medial tibial implant component can be independently designed and/or selected to maintain or alter the relative heights generated by different resection surfaces for each of the lateral and medial tibial plateaus.
  • the lateral tibial implant component can be thicker (e.g., 1 mm, greater than 1 mm, 2 mm, and/or greater than 2 mm thicker) or thinner (e.g., 1 mm, greater than 1 mm, 2 mm, and/or greater than 2 mm thinner) than the medial tibial implant component to maintain or alter, as desired, the relative height of the joint-facing surface of each of the lateral and medial tibial implant components.
  • the relative heights of the lateral and medial resection surfaces 6020 is maintained using lateral and medial implant components (and lateral and medial polyethylene layers or inserts) that have the same thickness.
  • the lateral implant component (and/or the lateral polyethylene layer or insert) can have a different thickness than the medial implant component (and/or the medial polyethylene layer or insert).
  • the thickness of one implant component can be different from the thickness of the other implant component.
  • Different medial and lateral tibial cut heights also can be applied with a one piece implant component, e.g., a monolithically formed, tibial implant component.
  • the tibial implant component and the corresponding resected surface of the patient's femur can have an angled surface or a step cut connecting the medial and the lateral surface facets.
  • FIGS. 29A to 29C depict three different types of step cuts separating medial and lateral resection cut facets on a patient's proximal tibia.
  • the bone-facing surface of the tibial implant component is selected and/or designed to match these surface depths and the step cut angle, as well as other optional features such as perimeter shape.
  • the medial tibial plateau facet can be oriented at an angle different than the lateral tibial plateau facet or it can be oriented at the same angle.
  • One or both of the medial and the lateral tibial plateau facets can be at an angle that is patient-specific, for example, similar to the original slope or slopes of the medial and/or lateral tibial plateaus, for example, in the sagittal plane.
  • the medial slope can be patient-specific, while the lateral slope is fixed or preset or vice versa, as exemplified in Table 3.
  • Patient-matched to medial plateau Not patient-matched, e.g., preset, fixed or intraoperatively adjusted
  • Not patient matched e.g. preset, fixed or Not patient-matched, e.g. preset, fixed or intraoperatively adjusted intraoperatively adjusted
  • the exemplary combinations described in Table 3 are applicable to implants that use two unicompartmental tibial implant components with or without metal backing, one medial and one lateral. They also can be applicable to implant systems that use a single tibial implant component including all plastic designs or metal backed designs with inserts (optionally a single insert for the medial and lateral plateau, or two inserts, e.g., one medial and one lateral), for example PCL retaining, posterior stabilized, or ACL and PCL retaining implant components.
  • the slope can be set via the alignment of the metal backed component(s).
  • the metal backed component(s) can have substantially no slope in their alignment, while the medial and/or lateral slopes or both are contained or set through the insert topography or shape.
  • FIGS. 30A-30D Various embodiments of such implants are disclosed in FIGS. 30A-30D.
  • Fig. 30D depicts one alternate embodiment of a metal backed component 17200 implanted with no significant slope.
  • the tibial insert topography is, however, asymmetrical, and, in this case either selected or designed to closely approximate the patient's native tibial slope. In this example, this is achieved by selecting or designing a tibial insert 17215 that is substantially thicker anterior when compared to posterior. The difference in insert height anteriorly and posteriorly results in a slope similar to the patient's slope.
  • the various embodiments described herein, and derivations thereof, can be applied to a medial plateau, a lateral plateau or combinations thereof or both.
  • various combinations of tilted and/or untilted inserts and/or tilted and/or untilted metal backed components can be utilized to achieve a wide variety of surgical corrections and/or account for a wide variation in patient anatomy and/or surgical cuts necessary for treating the patient.
  • the natural slope of a patient's tibia requires a nonuniform resection (i.e., the cut is non-planar across the bone or is tilted and non- perpendicular relative to the mechanical axis of the bone, whether medially-laterally, anterior-posteriorly, or any combination thereof) or the surgical correction creates such a non-uniform or tilted resection
  • one or more correction factors can be designed into the metal backed component, into the tibial insert, or into any combination of the two.
  • the slope can naturally or artificially be made to vary from one side of the knee to the other, or anterior to posterior, and the implant components can account for such variation.
  • the slope can preferably be between 0 and 7 degrees, but other embodiments with other slope angles outside that range can be used.
  • the slope can vary across one or both tibial facets from anterior to posterior. For example, a lesser slope, e.g. 0-1 degrees, can be used anteriorly, and a greater slope can be used posteriorly, for example, 4-5 degrees.
  • Variable slopes across at least one of a medial or a lateral tibial facet can be accomplished, for example, with use of burrs (for example guided by a robot) or with use of two or more bone cuts on at least one of the tibial facets.
  • two separate slopes can be used medially and laterally.
  • Independent tibial slope designs can be useful for achieving bone preservation.
  • independent slope designs can be advantageous in achieving implant kinematics that will be more natural, closer to the performance of a normal knee or the patient's knee.
  • the slope can be fixed, e.g. at 3, 5 or 7 degrees in the sagittal plane.
  • the slope, either medial or lateral or both can be patient-specific.
  • the patient's medial slope can be used to derive the medial tibial component slope and, optionally, the lateral component slope, in either a single or a two-piece tibial implant component.
  • the patient's lateral slope can be used to derive the lateral tibial component slope and, optionally, the medial component slope, in either a single or a two-piece tibial implant component.
  • a patient's slope typically is between 0 and 7 degrees.
  • a patient may show a medial or a lateral slope that is greater than 7 degrees.
  • the patient's medial slope has a higher value than 7 degrees or some other preselected threshold
  • the patient's lateral slope can be applied to the medial tibial implant component or to the medial side of a single tibial implant component.
  • the patient's medial slope can be applied to the lateral tibial implant component or to the lateral side of a single tibial implant component.
  • FIGS. 31 A and 31 B show exemplary flow charts for deriving a medial tibial component slope (FIG. 31 A) and/or a lateral tibial component slope (FIG. 31 B) for a tibial implant component.
  • the medial and lateral tibial plateau can be resected at the same angle.
  • a single resected cut or the same multiple resected cuts can be used across both plateaus.
  • the medial and lateral tibial plateau can be resected at different angles. Multiple resection cuts can be used when the medial and lateral tibial plateaus are resected at different angles.
  • the medial and the lateral tibia also can be resected at a different distance relative to the tibial plateau.
  • the two horizontal plane tibial cuts medially and laterally can have different slopes and/or can be accompanied by one or two vertical or oblique resection cuts, typically placed medial to the tibial plateau components.
  • FIGS. 32 and FIGS. 29A to 29C show several exemplary tibial resection cuts, which can be used in any combination for the medial and lateral plateaus.
  • the medial tibial implant component plateau can have a flat, convex, concave, or dished surface and/or it can have a thickness different than the lateral tibial implant component plateau.
  • the lateral tibial implant component plateau can have a flat, convex, concave, or dished surface and/or it can have a thickness different than the medial tibial implant component plateau.
  • the different thickness can be achieved using a different material thickness, for example, metal thickness or polyethylene or insert thickness on either side.
  • the lateral and medial surfaces are selected and/or designed to closely resemble the patient's anatomy prior to developing the arthritic state.
  • the height of the medial and/or lateral tibial component plateau can be determined based on the patient's femoral shape. For example, if the patient's lateral condyle has a smaller radius than the medial condyle and/or is located more superior than the medial condyle with regard to its bearing surface, the height of the tibial component plateau can be adapted and/or selected to ensure an optimal articulation with the femoral bearing surface.
  • the height of the lateral tibial component plateau can be adapted and/or selected so that it is higher than the height of the medial tibial component plateau. Since polyethylene is typically not directly visible on standard x-rays, metallic or other markers can optionally be included in the inserts in order to indicate the insert location or height, in particular when asymmetrical medial and lateral inserts or inserts of different medial and lateral thickness are used.
  • the height of the medial and/or lateral tibial component plateau e.g. metal only, ceramic only, metal backed with polyethylene or other insert, with single or dual inserts and single or dual tray configurations can be determined based on the shape of a corresponding implant component, for example, based on the shape of certain features of the patient's femoral implant component.
  • the height of the tibial implant component plateaus can be adapted and/or selected to ensure an optimal articulation with the bearing surface(s) of the femoral implant component.
  • the height of the lateral tibial implant component plateau can be adapted and/or selected to be higher than the height of the medial tibial implant component plateau.
  • a cutter can be used to cut a fixed coronal curvature into a tibial insert or all polyethylene tibia that is matched to or derived from a femoral implant or patient geometry.
  • the path and/or depth that the cutter is taking can be driven based on the femoral implant geometry or based on the patient's femoral geometry prior to the surgery.
  • Medial and lateral sagittal geometry can be the same on the tibial inserts or all poly tibia. Alternatively, each can be cut separately.
  • tibial poly geometry By adapting or matching the tibial poly geometry to the sagittal geometry of the femoral component or femoral condyle, a better functional result may be achieved. For example, more physiologic tibiofemoral motion and kinematics can be enabled. Alternatively, the path and/or depth that the cutter is taking can be driven based on the patient's tibial geometry prior to the surgery, optionally including estimates of meniscal shape. Medial and lateral sagittal geometry can be the same on the tibial inserts or all poly tibia.
  • each can be cut separately.
  • the tibial poly geometry to the sagittal geometry of the patient's tibial plateau, a better functional result may be achieved.
  • more physiologic tibiofemoral motion and kinematics can be enabled.
  • at least portions of the femoral sagittal J-curve can be matched to or derived from or selected based on the tibial implant geometry or the patient's tibial curvature, medially or laterally or combinations thereof.
  • the medial and/or the lateral component can include a trough.
  • the medial component can be dish shaped, while the lateral component includes a trough.
  • the lateral component can be dish shaped, while the medial component includes a trough.
  • the lateral component can be convex, while the medial
  • the component includes a trough.
  • the shape of the medial or lateral component can be patient derived or patient matched in one, two or three dimensions, for example as it pertains to its perimeter as well as its surface shape.
  • the convex shape of the lateral component can be patient derived or patient matched in one, two or three dimensions.
  • the trough can be straight.
  • the trough can also be curved.
  • the curvature of the trough can have a constant radius of curvature or it can include several radii of curvature.
  • the radii can be patient matched or patient derived, for example based on the femoral geometry or on the patient's kinematics.
  • FIGS. 33A through 33J show exemplary combinations of tibial tray designs.
  • FIGS. 34A through 34F include additional embodiments of tibial implant components that are cruciate retaining.
  • the tibial implant surface topography can be selected for, adapted to or matched to one or more femoral geometries.
  • the distance of the lowest point of the medial dish or trough to the lowest point of the lateral dish or trough can be selected from or derived from or matched to the femoral geometry, e.g. an intercondylar distance or an intercondylar notch width (see FIGS. 35G - 35K).
  • the tibial component(s) can be adapted to the femoral geometry, ensuring that the lowest point of the femoral bearing surface will mate with the lowest point of the resultant tibial bearing surface.
  • an exemplary femoral geometry may be determined or derived, and then a matching or appropriate tibial implant geometry and surface geometry can be derived from the femoral geometry (i.e., from anatomical or biomechanical or kinematic features in the sagittal and/or coronal plane of the femur) or from a combination of the femoral geometry with the tibial geometry.
  • a matching or appropriate tibial implant geometry and surface geometry can be derived from the femoral geometry (i.e., from anatomical or biomechanical or kinematic features in the sagittal and/or coronal plane of the femur) or from a combination of the femoral geometry with the tibial geometry.
  • multi-complex joint implants having three or more component support structures, such as the knee (i.e., patella, femur and tibia), elbow (humerus, radius and ulna), wrist (radius, ulna and carpals), and ankle (fibula, tibia, talus and calcaneus) can be modeled and repaired/replaced with components modeled, derived and manufactured incorporating features of two or more mating surfaces and underlying support structures of the native joint.
  • knee i.e., patella, femur and tibia
  • elbow humerus, radius and ulna
  • wrist radius, ulna and carpals
  • ankle fibula, tibia, talus and calcaneus
  • the slope for tibial cuts typically is between 0 and 7 or 0 and 8 degrees in the sagittal plane. Rarely, a surgeon may elect to cut the tibia at a steeper slope.
  • the slope can be selected or designed into a patient-specific cutting jig using a preoperative imaging test.
  • the slope can be similar to the patient's preoperative slope on at least one of a medial or one of a lateral side.
  • the medial and lateral tibia can be cut with different slopes.
  • the slope also can be different from the patient's preoperative slope on at least one of a medial or one of a lateral side.
  • tibial trays can have the following features, although other embodiments are possible: modular insert system (polymer); cast cobalt chrome; standard blanks (cobalt portion and/or modular insert) can be made in advance, then shaped patient-specific to order; thickness based on size (saves bone, optimizes strength); allowance for 1 -piece or 2-piece insert systems; and/or different medial and lateral fins.
  • the tibial cut height can differ medially and laterally, as shown in FIGS. 32 and FIGS. 29A to 29C.
  • the uncut lateral tibia can be at a different height, for example, higher or lower, than the uncut medial tibia.
  • the medial and lateral tibial cuts can be placed at a constant distance from the uncut medial and the uncut lateral tibial plateau, resulting in different cut heights medially or laterally.
  • they can be cut at different distances relative to the uncut medial and lateral tibial plateau, resulting in the same cut height on the remaining tibia.
  • the resultant cut height on the remaining tibia can be elected to be different medially and laterally.
  • independent design of the medial and lateral tibial resection heights, resection slopes, and/or implant component e.g., tibial tray and/or tibial tray insert
  • implant component can enhance bone perseveration on the medial and/or lateral sides of the proximal tibia as well as on the opposing femoral condyles.
  • the medial portion of a tibial implant may be higher or lower than the lateral tibial portion to compensate for different sizes of the medial and lateral femoral condyle.
  • This method can facilitate maintenance of a patient's normal J-curve and thus help preserve normal knee kinematics.
  • the effect may be achieved by offsetting the higher tibial articular surface to be the same height as the other compartment. If the condylar J- curve is offset by the same amount, the same kinematic motion can be achieved, as illustrated in FIG. 36.
  • the gray wheel 19500 (femoral condyle) and track 19510 (tibial implant surface) are offset by the same amount as the orange wheel 19520 and track 19530.
  • a similar motion path 19540 blue dotted curve
  • the tibial implant surface is desirably offset perpendicular to the surface, this will result in a new surface curvature that may be different than that of the other compartment. Offsetting the femoral J-curve by the corresponding amount desirably reduces the amount of bone to be removed from the femoral condyle.
  • a different tibial slope can be applied on the medial and the lateral side.
  • a fixed slope can be applied on one side, while the slope on the other side can be adapted based on the patient's anatomy.
  • a medial slope can be fixed at 5 degrees, while a lateral slope matches that of the patient's tibia.
  • two unicondylar tibial inserts or trays can be used.
  • a single tibial component can be used wherein said component does not have a flat, bone-facing surface, but includes, for example, an oblique portion to connect the medial to the lateral side substantially negatively-match resected lateral and medial tibial surfaces as shown, for example, in FIGS. 32 and FIGS. 29A to 29C.
  • Each of the two contact areas of the polyethylene insert of the tibial implant component that engage the femoral medial and lateral condyle surfaces can be any shape, for example, convex, flat, or concave, and can have any radii of curvature.
  • any one or more of the curvatures of the medial or lateral contact areas can include patient-specific radii of curvature.
  • one or more of the coronal curvature of the medial contact area, the sagittal curvature of the medial contact area, the coronal curvature of the lateral contact area, and/or the sagittal curvature of the lateral contact area can include, at least in part, one or more patient-specific radii of curvature.
  • the tibial implant component is designed to include one or both medial and lateral bearing surfaces having a sagittal curvature with, at least in part, one or more patient-specific radii of curvature and a standard coronal curvature.
  • the bearing surfaces on one or both of the medial and lateral tibial surfaces can include radii of curvature derived from (e.g., the same length or slightly larger, such as 0-10% larger than) the radii of curvature on the corresponding femoral condyle. Having patient- adapted sagittal radii of curvature, at least in part, can help achieve normal kinematics with full range of motion.
  • one or both tibial medial and lateral contact areas have a standard concave coronal radius that is larger, for example slightly larger, for example, between 0 and 1 mm, between 0 and 2 mm, between 0 and 4 mm, between 1 and 2 mm, and/or between 2 and 4 mm larger, than the convex coronal radius on the corresponding femoral component.
  • a standard or constant coronal radius on a femoral condyle with a matching standard or constant coronal radius or slightly larger on a tibial insert for example, with a tibial radius of curvature of from about 1 .05x to about 2x, or from about 1 .05x to about 1 .5x, or from about 1 .05x to about 1 .25x, or from about 1 .05x to about 1 .1 Ox, or from about 1 .05x to about 1 .06x, or about 1 .06x of the corresponding femoral implant coronal curvature.
  • the relative convex femoral coronal curvature and slightly larger concave tibial coronal curvature can be selected and/or designed to be centered to each about the femoral condylar centers.
  • one or both tibial medial and lateral concave curvatures can have a standard curvature slightly larger than the corresponding convex femoral condyle curvature, for example, between 0 and 1 mm, between 0 and 2 mm, between 0 and 4 mm, between 1 and 2 mm, and/or between 2 and 4 mm larger, than the convex sagittal radius on the corresponding femoral component.
  • the tibial radius of curvature for one or both of the medial and lateral sides can be from about 1 .1 x to about 2x, or from about 1 .2x to about 1 .5x, or from about 1 .25x to about 1 .4x, or from about 1 .30x to about 1 .35x, or about 1 .32x of the corresponding femoral implant sagittal curvature.
  • the depth of the curvature into the tibial surface material can depend on the height of the surface into the joint gap.
  • the height of the medial and lateral tibial component joint-facing surfaces can be selected and/or designed independently.
  • the medial and lateral tibial heights are selected and/or designed independently based on the patient's medial and lateral condyle height difference.
  • a threshold minimum or maximum tibial height and/or tibial insert thickness can be used.
  • a threshold minimum insert thickness of 6 mm is employed so that no less than a 6 mm medial tibial insert is used.
  • tibial trays can be designed with the following features, although other embodiments are possible: modular insert system (polymer); cast cobalt chrome; standard blanks (cobalt portion and/or modular insert) can be made in advance, then shaped patient-specific to order; thickness based on size (saves bone, optimizes strength); allowance for 1 -piece or 2-piece insert systems; and/or different medial and lateral fins.
  • modular insert system polymer
  • cast cobalt chrome cast cobalt chrome
  • standard blanks cobalt portion and/or modular insert
  • thickness based on size (saves bone, optimizes strength); allowance for 1 -piece or 2-piece insert systems; and/or different medial and lateral fins.
  • Various tibial tray embodiments can include the following features, although other embodiments are possible: modular insert system (polymer); cast cobalt chrome; standard blanks (cobalt portion and/or modular insert) can be made in advance, then shaped patient-specific to order; thickness based on size (saves bone, optimizes strength); allowance for 1 -piece or 2-piece insert systems; and/or different medial and lateral fins.
  • a locking mechanism for securing a tibial insert into a tibial tray can be designed and manufactured as an integral portion of the tibial tray.
  • the locking mechanism can be significantly smaller than the upper surface of the tray, to allow for perimeter matching of the tray, whereby subsequent machining and/or processing of the outer periphery and upper portion of the tibial tray (to patient-matched dimensions) will not significantly degrade or otherwise affect the locking mechanism (i.e., the final patient-matched perimeter of the implant does not cut-into the lock).
  • the locking mechanism may extend along the entire upper surface of the tibial tray, whereby perimeter matching of the tray results in removal of some portion of the locking mechanism, yet the remainder of the locking mechanism is still capable of retaining the tibial insert on the tibial tray (i.e., the final patient-matched perimeter of the implant cuts into some of the lock structure, but sufficient lock structure remains to retain the insert in the tray).
  • Such embodiments may have locking mechanisms preformed in a library of pre-formed tibial tray blanks.
  • one or more locking mechanism designs may be incorporated into the implant design program, with an appropriate locking mechanism design and size chosen at the time of implant design, and ultimately formed into (or otherwise attached to) a tibial tray (chosen or designed to match patient anatomy) during the process of designing, manufacturing and/or modifying the implant for use with the specific patient.
  • Such design files can include CAD files or subroutines of locking mechanism of various sizes, shaped and/or locking features, with an appropriate locking mechanism chosen at an appropriate time.
  • the design program can ultimately analyze the chosen/designed lock and locking mechanism to confirm that the final lock will be capable of retaining the insert within the tray under loading and fatigue conditions, and alerting (or choosing an alternative design) if FEA or other analyses identifies areas of weakness and/or concern in the currently-chosen design.
  • Standard blank tibial trays and/or inserts can be prepared in multiple sizes, e.g., having various AP dimensions, ML dimensions, and/or stem and keel dimensions and configurations.
  • the stem can be 13 mm in diameter and 40 mm long and the keel can be 3.5 mm wide, 15 degrees biased on the lateral side and 5 degrees biased on the medial side.
  • the step and keel can be larger, smaller, or have a different
  • FIGS. 37A to 37C show exemplary steps for altering a blank tibial tray and a blank tibial insert to each include a patient-adapted profile, for example, to substantially match the profile of the patient's resected tibial surface.
  • standard cast tibial tray blanks and standard machined insert blanks e.g., having standard locking mechanisms
  • the blank tray and insert can be finish machined to match or optimize one or more patient-specific features based on patient-specific data.
  • the patient-adapted features machined into the blanks can include for example, a patient-specific perimeter profile and/or one or more medial coronal, medial sagittal, lateral coronal, lateral sagittal bone-facing insert curvatures.
  • FIG. 37C illustrates a finished tibial implant component that includes a patient-specific perimeter profile and/or one or more patient-adapted bone-facing insert curvatures.
  • FIGS. 38A to 38D show four different exemplary tibial implant profiles, for example, having different medial and lateral condyle perimeter shapes that generally match various different relative medial and lateral condyle perimeter dimensions.
  • a tibial tray and/or insert can be selected (e.g., preoperatively or intraoperatively) from a collection or library of implants for a particular patient (i.e., to best-match the perimeter of the patient's cut tibial surface) and implanted without further alteration to the perimeter profile.
  • these different tibial tray and/or insert perimeter profiles can serve as blanks.
  • one of these tibial tray and/or insert profiles can be selected preoperatively from a library (e.g., an actual or virtual library) for a particular patient to best-match the perimeter of the patient's cut tibial surface. Then, the selected implant perimeter can be designed or further altered based on patient-specific data, for example, to substantially match the perimeter of the patient's cut tibial surface.
  • a library e.g., an actual or virtual library
  • the design of a bone cement pocket or pockets of an implant component also may include features that are patient-specific and/or optimized according to one or more of the parameters discussed above.
  • FIGS. 39A and 39B show bone cement pockets in a component of certain
  • each section or facet of the bone-facing surface of the component can have an independent cement pocket.
  • One or more of the cement pockets can be offset from the periphery by 2 mm or more.
  • Each pocket can have a maximum depth of less than 0.9 mm, for example, 0.5 mm or less.
  • FIG. 40G depicts a sizing tool or spacer 18150 for use in adjusting and optimizing alignment, tension, balance, and position (e.g., as described in Table 4) during a knee implant surgery (see FIGS. 40A-40K).
  • the sizing tool 18150 may be one of a series of spacers utilized to determine an optimal size and shape for a tibial tray insert for ultimate placement in the knee joint.
  • each spacer corresponds to one or more of a plurality of tibial inserts in the surgical kit, although various embodiments could include one or more "adjustable" spacers having detents or other mechanisms that facilitate adjustment and
  • a first side 18160 of the spacer has a first height and/or alignment
  • a second side 18170 of the spacer has a second height and/or alignment (allowing for medial/lateral distal femoral component bearing surface or cut asymmetry).
  • the superior surfaces of the spacer desirably engage the cut surface of the femur and the inferior surfaces engage the cut surfaces of the tibia.
  • the various spacers can be patient-adapted to fit the particular patient, and may incorporate perimeter matching or other indicia to correspond to some or all of the perimeter of the cut and/or uncut bone surfaces (i.e., the outer perimeter of the jig matches the outer perimeter of the bone surfaces - cut and/or uncut).
  • the spacers can include a resection surface to guide a subsequent surgical bone cut. Desirably, the thinnest insert that properly balances the knee will be chosen, reducing the chance for "overstuffing" of the knee joint. Table 4: Exemplary approach options for optimizing soft-tissue tension, ligament tension, ligament balance, and/or flexion and extension gap
  • Tibial component profile e.g., convexity, concavity, trough, radii of curvature
  • Lateral tibial insert or component or composite profile e.g.
  • FIG. 40G depicts a spacer being inserted in extension between the femur and tibia.
  • FIG. 41 depicts a flexion gap balancer block for use in a knee brought into flexion.
  • one or more balancer blocks 18200 can be placed between the cut surface of the tibia and the uncut posterior femoral condyles of the femur (with the femur in flexion) until proper alignment and orientation of the flexion gap is reached, and then an AP cut guide 18210 is positioned relative to the balancer block 18200 (at the surgeon's preference) and then the guide 18200 is pinned in place and the block 18200 removed.
  • the guide 18210 includes a pair of cutting guides 18220, 18230 which can be used by the surgeon to align the posterior femoral cuts.
  • the cuts may be asymmetric, as desired, typically representing asymmetric posterior cut locations on the implant, and they allow fine-tuning of the external femoral rotation of the joint replacement.
  • the outer perimeters of the various jigs and blocks may matching some or all of the perimeter (cut and/or uncut) of the adjacent bone or bones, or may otherwise incorporate indicia identifying the margins of such adjacent surfaces.
  • FIGS. 42A, 42B and 42C depict an additional balancing technique to properly align a desired external rotation to the knee prosthesis prior to insertion of a tibial tray and tibial insert.
  • FIG. 42A depicts the spacer of FIG. 40G in a desired position between a cut femur and cut tibia.
  • FIG. 42B depicts a flexion block 18300 between the cut femur (now incorporating a femoral implant) and the cut tibial surface.
  • the first and second sides of this block are positioned and aligned such that, when the replacement femoral condyle surfaces contact the block, the implant "tilts" or externally rotates the femoral component a desired amount, which in this example is approximately 5.77 degrees (FIG. 42C).
  • the surgeon can choose a corresponding tibial spacer (not shown) and tibial tray combination that achieves this same desired alignment for the femoral component.
  • articular implants including, but not limited to, knee-joint implants, hip-joint implants, shoulder-joint implants, and spinal implants (e.g., intervertebral implants and facet joint implants), as well as related surgical tools (e.g., guide tools) and methods.
  • FIGS. 43A-43M Exemplary traditional implants are illustrated in FIGS. 43A-43M.
  • FIGS. 43A and 43B illustrate exemplary traditional knee-joint implants as described, for example, in US Patent No. 5,824,105 and 5,133,758, respectively;
  • FIGS. 43C-43G illustrate traditional hip-joint implants, including Austin Moore-type, Thompson-type, and Bipolar hip-type prostheses;
  • FIGS. 43H-43J illustrate traditional shoulder-joint implants as described, for example, in US Patent No. 7,175,663;
  • FIGS. 43K-43M illustrate traditional spinal implants, as described, for example, in US Patent No. 7,166,129 and at the web site, www.facetsolutions.com/AFRSproduct.html.
  • An initial step in assessing one or more anatomical features of a patient is to obtain information about the size, shape and/or condition of the relevant patient anatomy.
  • this process typically includes obtaining one or more images of the patient's anatomy of interest (which can include a joint and/or other relevant patient anatomy - i.e., adjacent anatomical areas and or other features of interest) using, for example, non-invasive imaging modalities or scans (including those previously described, as well as those known in the art).
  • the raw electronic image data can be used to create one or more representations or "models" of the patient's anatomy. These representations can include electronic models as well as 2-Dimensional images and/or 3-Dimensional physical
  • the models can include anatomic reference points and/or limb alignments, including alignment angles within the same and between different joints as well as comparisons to simulated normal limb alignment(s). Any anatomic features related to the misalignment can be selected and imaged.
  • the imaging test can include data from at least one of, or several of, a hip joint, knee joint and ankle joint. The imaging test can be obtained in lying, prone, supine or standing position. The imaging test can include only the target joint, or both the target joint and also selected data through one or more adjoining joints.
  • the reference points can be located on or in the joint that will receive the patient-specific implant.
  • the reference points can include weight- bearing surfaces or locations in or on the joint, a cortex in the joint, and/or an endosteal surface of the joint.
  • the reference points also can include surfaces or locations outside of but related to the joint.
  • reference points can include surfaces or locations functionally related to the joint.
  • reference points can include one or more locations ranging from the hip down to the ankle or foot.
  • the reference points also can include surfaces or locations homologous to the joint receiving the implant.
  • reference points can include one or more surfaces or locations from the contralateral knee, hip, or shoulder joint.
  • one or more mechanical or anatomical axes, angles, planes or combinations thereof can be determined.
  • such axes, angles, and/or planes can include, or be derived from, one or more of a Whiteside's line, Blumensaat's line, transepicondylar line, femoral shaft axis, femoral neck axis, acetabular angle, lines tangent to the superior and inferior acetabular margin, lines tangent to the anterior or posterior acetabular margin, femoral shaft axis, tibial shaft axis, transmalleolar axis, posterior condylar line, tangent(s) to the trochlea of the knee joint, tangents to the medial or lateral patellar facet, lines tangent or perpendicular to the medial and lateral posterior condyles, lines tangent or perpendicular to a central weight-
  • estimating a mechanical axis, an angle, or plane also can be performed using image data obtained through two or more joints, such as the knee and ankle joint, for example, by using the femoral shaft axis and a centerpoint or other point in the ankle, such as a point between the malleoli.
  • the imaging test can include acquiring data through at least one of, or several of, a hip joint, knee joint or ankle joint.
  • a mechanical axis can be determined.
  • the centerpoint of the hip knee and ankle can be determined.
  • a mechanical axis can be determined in the coronal plane.
  • the position of the knee relative to said mechanical axis can be a reflection of the degree of varus or valgus deformity.
  • the same determinations can be made in the sagittal plane, for example to determine the degree of genu antecurvatum or recurvatum. Similarly, any of these determinations can be made in any other desired planes, in two or three dimensions.
  • the raw image information and models thereof can be used to simulate biomotion of one or more joints and/or extremities, such as a knee joint, or a knee and ankle joint, or a hip, knee and/or ankle joint.
  • a computer can model the existing patient anatomy for various uses, including (1 ) to create patient-specific imaging data and/or models thereof, (2) to identify deficiencies in the existing anatomy, (3) to determine if replication of the existing patient anatomy would create a desired or acceptable outcome for the joint repair/replacement procedure, (4) to derive, identify and/or plan modifications or alterations to the existing anatomy to create one or more desired anatomical features for the patient's anatomy, (5) to design joint repair/replacement implant components, surgical tools and surgical procedures for treating the relevant patient anatomy, and/or (6) to plan surgical repair and replacement procedures for display to and/or further use by surgeons and/or patients.
  • patient-specific kinematic data such as obtained in a gait lab.
  • patient-specific navigation data for example generated using a surgical navigation system, image guided or non-image guided can be fed into the computer program.
  • This kinematic or navigation data can, for example, be generated by applying optical or RF markers to the limb and by registering the markers and then measuring limb movements, for example, flexion, extension, abduction, adduction, rotation, and other limb movements.
  • other data including anthropometric data may be added for each patient. These data can include but are not limited to the patient's age, gender, weight, height, size, body mass index, and race. Desired limb alignment and/or deformity correction can also be added into the model.
  • a patient-specific biomotion model can be derived that includes combinations of parameters.
  • the biomotion model can simulate various activities of daily life including normal gait, stair climbing, descending stairs, running, kneeling, squatting, sitting and any other physical activity.
  • the biomotion model can start out with standardized activities, typically derived from reference databases. These reference databases can be, for example, generated using biomotion measurements using force plates and motion trackers using radiofrequency or optical markers and video equipment.
  • Such measurements can potentially yield extremely useful data on the alignment and/or movement of the joint and surrounding structures (as well as the loading conditions of the various joint components) - information which may be difficult to obtain or model from standard imaging techniques (i.e., sitting or lying X-rays, CT-scans and/or MRI imaging).
  • load- bearing measurements can include imaging of the patient standing, walking and/or carrying loads of varying sizes and/or weights, as well as other activity appropriate and/or relevant to the joint and/or extremity of interest.
  • Such simulations can include virtually modeling the alignment and load bearing condition of the joint and
  • Such simulations can be used to obtain valuable anatomical, biomechanical and kinematic data including the loaded condition of various joint components, component positions, component movement, joint and/or surrounding tissue anatomical or biomechanical constraints or limitations, as well as estimated mechanical axes in one or more directions (i.e., coronal, sagittal or combinations thereof). This information could then be utilized (alone or in combination with other data described herein) to design various features of a joint resurfacing/replacement implant. This method can be incorporated in the various embodiments described herein as additional patient measurement and
  • anatomical/joint modeling and design data This analysis is applicable to many different joints, including those of the medial condyle, a lateral condyle, a trochlea, a medial tibia, a lateral tibia, the entire tibia, a medial patella, a lateral patella, an entire patella, a medial trochlea, a central trochlea, a lateral trochlea, a portion of a femoral head, an entire femoral head, a portion of an acetabulum, an entire acetabulum, a portion of a glenoid, an entire glenoid, a portion of a humeral head, an entire humeral head, a portion of an ankle joint, an entire ankle joint, and/or a portion or an entire elbow, wrist, hand, finger, spine, or facet joint.
  • the biomotion model can then be individualized with use of patient-specific information including at least one of, but not limited to the patient's age, gender, weight, height, body mass index, and race, the desired limb alignment or deformity correction, and the patient's imaging data, for example, a series of two- dimensional images or a three-dimensional representation of the joint for which surgery is contemplated.
  • patient-specific measurements and information that be used in the evaluation can include, for example, joint kinematic measurements, bone density measurements, bone porosity measurements, identification of damaged or deformed tissues or structures, and patient information, such as patient age, weight, gender, ethnicity, activity level, and overall health status.
  • patient-specific measurements may be compared, analyzed of otherwise modified based on one or more "normalized" patient model or models, or by reference to a desired database of anatomical features of interest. For example, a series of patient-specific femoral measurements may be compiled and compared to one or more exemplary femoral or tibial measurements from a library or other database of "normal" femur
  • femoral shape length, width, height, of one or both condyles, intercondylar shapes and dimensions, trochlea shape and dimensions, coronal curvature, sagittal curvature, cortical/cancellous bone volume and/or quality, etc., and a series of recommendations and/or modifications may be accomplished.
  • Any parameter mentioned in the specification and in the various Tables throughout the specification including anatomic, biomechanical and kinematic parameters can be utilized, not only in the knee, but also in the hip, shoulder, ankle, elbow, wrist, spine and other joints.
  • Such analysis may include modification of one or more patient-specific features and/or design criteria for the implant to account for any underlying deformity reflected in the patient-specific measurements.
  • the various anatomical features may be differently "weighted" during the comparison process (utilizing various formulaic weightings and/or mathematical algorithms), based on their relative importance or other criteria chosen by the designer/programmer and/or physician.
  • Table 5 Exemplary patient-specific measurements of biological features that can be used in the creation of a model and/or in the selection and/or design of an implant component
  • Joint gap differential e.g., medial to lateral Medullary cavity Shape in one or more dimensions
  • Subchondral bone Shape in one or more dimensions
  • Angle e.g., resection cut angle
  • Cortical bone Shape in one or more dimensions
  • Angle e.g.. resection cut angle
  • Endosteal bone Shape in one or more dimensions
  • Angle e.g., resection cut angle
  • Cartilage Shape in one or more dimensions
  • Angle e.g.. resection cut angle
  • Intercondylar notch Shape in one or more dimensions
  • Angle e.g., resection cut angle
  • Thickness in one or more locations Anatomical feature Exemplary measurement
  • Trochlear angle e.g. groove angle in one or more locations
  • Resection surface at an intended resection level Central trochlea - 2D and/or 3D shape of a portion or all
  • Trochlear angle e.g. groove angle in one or more locations
  • Resection surface at an intended resection level Entire tibia - 2D and/or 3D shape of a portion or all
  • Bearing surface radii e.g.. e.g.. relative radii medial and lateral
  • Angle e.g., resection cut angle
  • Angle e.g.. resection cut angle
  • Resection surface at an intended resection level Acetabulum - 2D and/or 3D shape of a portion or all
  • Resection surface at an intended resection level Humeral head - 2D and/or 3D shape of a portion or all
  • Thickness in one or more locations Anatomical feature Exemplary measurement
  • Resection surface at an intended resection level Humeral shaft - 2D and/or 3D shape of a portion or all
  • Resection surface at an intended resection level Elbow - 2D and/or 3D shape of a portion or all
  • Thickness in one or more locations Anatomical feature Exemplary measurement
  • Angle e.g.. resection cut angle
  • Angle e.g., resection cut angle
  • Angle e.g.. resection cut angle
  • models can be generated to show defects of interest in a patient's joint.
  • a model or set of models of a patient's joint can be generated showing defects of interest and, optionally, another model or set of models can be generated showing no defects (e.g., as defect and reference, or before and after models).
  • the reference points, measurements and/or models described herein can be processed using mathematical functions to derive virtual, corrected features, which may represent a restored, ideal or desired feature from which a patient-adapted implant component can be designed.
  • one or more features, such as surfaces or dimensions of a biological structure can be modeled, altered, added to, changed, deformed, eliminated, corrected and/or otherwise manipulated (collectively referred to herein as "variation" of an existing surface or structure within the joint). While it is described in the knee, these embodiments can be applied to any joint or joint surface in the body, e.g. a knee, hip, ankle, foot, toe, shoulder, elbow, wrist, hand, and a spine or spinal joints.
  • the various anatomical features of any joint can be measured and then compared/modified based on a database of "healthy" or otherwise appropriate measurements of appropriate joints, including those of the medial condyle, a lateral condyle, a trochlea, a medial tibia, a lateral tibia, the entire tibia, a medial patella, a lateral patella, an entire patella, a medial trochlea, a central trochlea, a lateral trochlea, a portion of a femoral head, an entire femoral head, a portion of an acetabulum, an entire acetabulum, a portion of a glenoid, an entire glenoid, a portion of a humeral head, an entire humeral head, a portion of an ankle joint, an entire ankle joint, and/or a portion or an entire elbow, wrist, hand,
  • the design and placement of the tibial implant i.e., size, shape, thickness and/or tibial tray rotation angle and orientation
  • the design and placement of a femoral implant i.e., size, shape, thickness and/or femoral component rotation angle and orientation
  • the design and placement of a other implant components i.e., size, shape, thickness and/or component rotation angle and orientation
  • acetabular or femoral head resurfacing or replacement glenoid or humeral head resurfacing or replacement, elbow resurfacing or replacement, wrist resurfacing or replacement, hand resurfacing or replacement, ankle resurfacing or replacement, for resurfacing or replacement can be more accurately determined.
  • one or more combinations of model features can be combined into one or models or sets of models that convey desired information to the surgeon or clinician.
  • patient-specific bone models can be combined with any number of defects or defect types, any number of resection cuts, any number of drill holes, any number of axes, any number of guide tools, and/or any number of implant components to convey as much information as desired to the surgeon or clinician.
  • the patient-specific bone model can model any biological structure, for example, any one or more (or portion of) a femoral head and/or an acetabulum; a distal femur, one or both femoral condyle(s), and/or a tibial plateau; a trochlea and/or a patella; a glenoid and/or a humeral head; a talar dome and/or a tibial plafond; a distal humerus, a radial head, and/or an ulna; and a radius and/or a scaphoid.
  • Defects that can be combined with a patient-specific bone model can include, for example, osteophytes, voids,
  • articular shape defects e.g., rounded or flattened articular surfaces or surface portions
  • varus or valgus deformities or any other deformities known to those in the art.
  • the anatomical data, modified data and/or models may then be utilized to choose or design an appropriate implant to match the modified features, and a final verification operation may be accomplished to ensure the chosen implant is acceptable and appropriate to the original unmodified patient-specific measurements (i.e., the chosen implant will ultimately "fit" the original patient anatomy).
  • the thicknesses of one or more implant components or portions of one or more implant components can be selected or adapted or designed based on one or more geometric features of a patient or patient weight or height or BMI or other patient specific characteristics, e.g. gender, lifestyle, activity level etc.
  • This selection or adaptation or design can be performed for any implant component in a knee, hip, ankle, shoulder, elbow, wrist, spine or other human joint.
  • the fit between the implant(s) and the implantation site is evaluated.
  • the implant can be available in a range of different dimensions, sizes, shapes and thicknesses. Different dimensions, sizes, shapes and thicknesses can be available for a medial condyle, a lateral condyle, a trochlea, a medial tibia, a lateral tibia, the entire tibia, a medial patella, a lateral patella, an entire patella, a medial trochlea, a central trochlea, a lateral trochlea, a portion of a femoral head, an entire femoral head, a portion of an acetabulum, an entire acetabulum, a portion of a glenoid, an entire glenoid, a portion of a humeral head, an entire humeral head, a portion of an ankle joint, an entire ankle joint, and/or a portion
  • the bone-facing surface of an implant component includes multiple surfaces, also referred to herein as bone cuts.
  • One or more of the bone cuts on the bone-facing surface of the implant component can be selected and/or designed to substantially negatively-match one or more surfaces of the patient's bone.
  • the surface(s) of the patient's bone can include bone, cartilage, or other biological surfaces.
  • one or more of the bone cuts on the bone-facing surface of the implant component can be designed to substantially negatively-match (e.g., the number, depth, and/or angles of cut) one or more resected surfaces of the patient's bone.
  • the bone-facing surface of the implant component can include any number of bone cuts, for example, two, three, four, less than five, five, more than five, six, seven, eight, nine or more bone cuts.
  • the bone cuts of the implant component and/or the resection cuts to the patient's bone can include one or more facets on corresponding portions of an implant component.
  • the facets can be separated by a space or by a step cut connecting two corresponding facets that reside on parallel or non-parallel planes.
  • an implant component design or selection can depend, at least in part, on a threshold minimum implant component thickness.
  • the threshold minimum implant component thickness can depend, at least in part, on patient-specific data, such as condylar width, femoral transepicondylar axis length, and/or the patient's specific weight.
  • patient-specific data such as condylar width, femoral transepicondylar axis length, and/or the patient's specific weight.
  • the threshold implant thickness, and/or any implant component feature can be adapted to a particular patient based on a combination of patient-specific geometric data and on patient- specific anthropometric data. This approach can apply to any implant component feature for any joint, for example, the knee, the hip, or the shoulder.
  • Any implant component can be selected and/or adapted in shape so that it stays clear of important ligament structures.
  • Imaging data can help identify or derive shape or location information on such ligamentous structures.
  • the lateral femoral condyle of a unicompartmental, bicompartmental or total knee system can include a concavity or divot to avoid the popliteus tendon.
  • Imaging data can be used to design a tibial component (all polyethylene or other plastic material or metal backed) that avoids the attachment of the anterior and/or posterior cruciate ligament; specifically, the contour of the implant can be shaped so that it will stay clear of these ligamentous structures.
  • a safety margin e.g.
  • the glenoid component can include a shape or concavity or divot to avoid a subscapularis tendon or a biceps tendon.
  • the femoral component can be selected or designed to avoid an iliopsoas or adductor tendons.
  • a change made to a femoral bone cut based on patient-specific biomotion data can be referenced to or linked with a concomitant change to a bone cut on an opposing tibial surface, for example, if less femoral bone is resected, the computer program may elect to resect more tibial bone.
  • a femoral implant shape is changed, for example on an external surface, this can be accompanied by a change in the tibial component shape.
  • a tibial implant shape is changed, for example on an external surface, this can be accompanied by a change in the femoral component shape. This is, for example, particularly applicable when at least portions of the femoral bearing surface negatively-match the tibial joint-facing surface.
  • a patellar component radius is widened, this can be accompanied by a widening of an opposing trochlear bearing surface radius, or vice-versa
  • hip and/or shoulder implants can apply for hip and/or shoulder implants.
  • a hip if a femoral implant shape is changed, for example on an external surface, this can be accompanied by a change in an acetabular component shape. This is, for example, applicable when at least portions of the acetabular bearing surface negatively-match the femoral joint-facing surface.
  • a shoulder if a glenoid implant shape is changed, for example on an external surface, this can be accompanied by a change in a humeral component shape. This is, for example, particularly applicable when at least portions of the humeral bearing surface negatively-match the glenoid joint-facing surface, or vice-versa.
  • Similar matching of polyethylene or other plastic shape to opposing metal or ceramic component shape can be performed in the shoulder, e.g. with a glenoid component, or in a hip, e.g. with an acetabular cup, or in an ankle, e.g. with a talar component.
  • edge matching, designing, selecting or adapting implants including, optionally lock features, can be performed for implants used in any joint of the body.
  • Imaging tests available for edge matching, designing, selecting or adapting implants include CT, MRI, radiography, digital tomosynthesis, cone beam CT, ultrasound, laser imaging, isotope based imaging, SPECT, PET, contrast enhanced imaging for any modality, and any other imaging modality known in the art and developed in the future.
  • Various examples herein describe exemplary processes for selecting and/or designing implants, including patient-adapted total knee implants, as well as knee implants having one or more patient-specific and/or patient-engineered based on patient-specific data.
  • the steps described in these processes can be performed in any order and can be performed more than once in a particular process. For example, one or more steps can be reiterated and refined a second, third, or more times, before, during, or after performing other steps or sets of steps in the process.
  • processes may specifically describe steps for selecting and/or designing specific implants, such as patient-specific total knee implants, they can be adapted to design other embodiments, for example, patient-adapted bicompartmental knee implants, unicompartmental knee implants, and implants for shoulders and hips, vertebrae, and other joints.
  • the various exemplary processes described herein yield both predetermined surgical resection designs for altering articular surfaces of a patient's bones during surgery and designs for implants that specifically fit the patient, for example, following the surgical bone resectioning.
  • the implant selection and/or design which can include manufacturing or machining the implant to the selected and/or designed specifications using known techniques, includes one or more patient-engineered bone-facing surfaces that negatively-match the patient's resected bone surface.
  • the implant also can include other features that are patient- adapted, such as minimal implant thickness, articular geometry, and kinematic design features. This process can be applied to various joint implants and to various types of joint implants.
  • this design process can be applied to a total knee, cruciate retaining, posterior stabilized, and/or ACL/PCL retaining knee implants, bicompartmental knee implants, unicompartmental knee implants, and other joint implants, for example, for the shoulder, hip, elbow, spine, or other joints.
  • the thickness of an acetabular cup, either metal backing or polyethylene or ceramic or other insert can be adapted based on the patient's geometry, e.g. depth of the actebular fossa, AP, ML, SI dimensions or other parameters including femoral parameters.
  • any material known in the art can be used for any of the implant systems and component described in the various embodiments including, but not limited to metal, metal alloys, combinations of metals, plastic, polyethylene, cross- linked polyethylene's or polymers or plastics, pyrolytic carbon, nanotubes and carbons, as well as biologic materials.
  • Any fixation techniques and combinations thereof known in the art can be used for any of the implant systems and component described in the foregoing embodiments, for example including, but not limited to cementing techniques, porous coating of at least portions of an implant component, press fit techniques of at least a portion of an implant, ingrowth techniques, etc.
  • any of the implant components for a knee, hip, ankle, shoulder, elbow or wrist or other joint can be formed or adapted based on a pre-existing blank.
  • an imaging test e.g., a CT or MRI
  • information for example, about the shape or dimensions of the acetabular fossa, acetabulum or glenoid as well as any other portions of the joint.
  • Various dimensions or shapes of the joint can be determined and a pre-existing blank acetabular or glenoid component can then be selected.
  • the shape of the pre-existing blank acetabular or glenoid component can then be adapted to the patient's shape, for example, by selectively removing material, e.g. with a machining or cutting or abrasion or other process, or by adding material.
  • the shape of the blank will generally be selected to be smaller than the target anatomy when material is added to achieve the patient adapted or patient specific implant features or surfaces.
  • the shape of the blank will generally be selected to be larger than the target anatomy when material is removed to achieve the patient adapted or patient specific implant features or surfaces.
  • a blank may initially be designed, manufactured and/or cast (or other created using other processes known in the art) to be suitable for use in creating a specific implant component in a specific joint, and/or the blank may be created to be suitable for use in creating a one or more implant components within a single joint, and/or the blank may be created to be suitable for use in creating one or more implant components for multiple joints, including within opposing similar joints in a patient as well as within dissimilar joints (i.e., used to create a tibial joint implant for the knee as well as a talar joint implant for an ankle) within a patient or group of patients.
  • An outer, bone facing component can be adapted to or matched to the patient's anatomic features using a blank in this manner.
  • an insert can be adapted or shaped based on the patient's anatomic features in one or two or three dimensions.
  • a standard insert e.g. with a standard locking mechanism into the outer component, can be adapted so that its outer rim will not overhang the patient's anatomy, e.g. a glenoid rim, before or after a surgical alteration such as a cutting or reaming.
  • the surgical alteration can, in this example as well as in many of the foregoing and following embodiments, be simulated on a computer and the insert blank can then be shaped based on the result of the simulation.
  • a glenoid insert as well as a metal backing can be adapted, e.g. machined, so that its perimeter will match the glenoid rim in at least a portion either before or after the surgical alteration of the glenoid. Similar adaptations are possible in any other joint, including the hip, knee, ankle, elbow and wrist.
  • the implant components can be attached to the underlying bone, if desired.
  • Any attachment mechanism known in the art can be used, e.g. pegs, fins, keels, stems, anchors, pins and the like.
  • the attachment mechanisms can be standard in at least one of shape, size and location.
  • any peg, keel or other fixation features of acetabular or glenoid or femoral or tibial components or implant components in any other joint can be designed, adapted, shaped, changed or optimized relative to the patient's geometry, e.g. relative to the adjacent cortex or, for example, the center of a medullary cavity or other anatomic or geometric features.
  • a minimum implant component thickness can be engineered based on, or together with, other patient-engineered dimensions or features of the implant component, for example, one or more of implant component size, implant component condyle width, and one or more implant component surface curvatures. As discussed elsewhere, this portion of an implant component could show a highest stress load, as exemplified by FEA or similar analysis.
  • the minimum implant component thickness for this or any portion of the implant component can be engineered based on one or more factors related to stress load, for example: the size of the patient; the size of the patient's femur; the size of the patient's condyle; the size of the patient-engineered implant component; the size of the implant component condyle; and the implant component's joint-facing surface curvature in the region that is opposite the intersection of the distal bone cut and posterior bone cut.
  • a patient-specific minimum implant thickness can be engineered from patient-specific data, such as image data, and designed into the patient-adapted implant. This allows for minimal bone to be resected in the implant procedure and thereby can help to maximize bone preservation for any particular patient.
  • a subsequent knee implant can be a primary knee implant procedure, rather than a revision procedure.
  • the above embodiments are not only applicable to knee implants, but are applicable to implants in other parts of the body, e.g. an acetabulum, a femoral head, a glenoid, a humeral head, an elbow joint, a wrist joint, an ankle joint, a spine etc.
  • the sagittal and/or coronal curvatures of a patient's condyle can be determined from image data by assessing the surface of the condyle in a
  • the curvature(s) also can be assessed in an axial plane, for example for a patella, a trochlea, a glenoid, or an acetabulum.
  • a patient's J-curve can be determined independently for lateral and medial condyles.
  • one or both of the patient's lateral and medial condylar J-curves can be applied to one or more sections of a femoral implant component's medial and/or lateral J-curves.
  • the distal point of the lateral condyle through a range of motion 3810 and the distal point of the medial condyle through a range of motion 3820 can be assessed in an axial plane, for example for a patella, a trochlea, a glenoid, or an acetabulum.
  • a patient's J-curve can be determined independently for lateral and medial condyles.
  • the patient's J-curve can lie in more than one plane and more than one plane can be used to transfer and apply the J-curve to the implant component, for example, such that the J-curve lies in one plane for a portion and then angles away from that plane for a portion.
  • one or both of the implant component's condylar J-curves or portions thereof can match the patient's J-curve planar orientation.
  • corresponding medial and lateral planes that include portions of the patient's medial and lateral J-curves, respectively can be non-parallel to each other (e.g., angled toward each other anteriorly) or otherwise angled relative to an anatomical feature (e.g., the epicondylar axis, femoral mechanical axis, trochlear J-curve, and/or some other feature).
  • the corresponding J-curve portions of the femoral implant component and, optionally, the tibial implant component can be designed to match this planar orientation.
  • the J-curve or portions thereof e.g., the distal and/or posterior load-bearing portions
  • the J-curve or portions thereof can match the patient's J-curve in a sagittal direction or in both a sagittal and coronal direction.
  • a first direction can be one of an AP, ML, SI, sagittal, coronal, axial or oblique direction.
  • a second direction, different from the first direction can be one of an AP, ML, SI, sagittal, coronal, axial or oblique direction.
  • a third direction can be one of an AP, ML, SI, sagittal, coronal, axial or oblique direction.
  • the three directions can be perpendicular to each other or can be oriented at any other angle.
  • the angles of orientation of the three directions can be anatomy derived, e.g. an articular surface plane of a glenoid, humeral head, acetabulum or femoral head, or biomechanical or kinematic derived, e.g.
  • Various concepts associated with the configuration of articular surfaces also apply to other aspects of knee prosthesis, such as matching a patella and trochlear groove, as well as to other joints such as the placement of weight bearing or other articulating surfaces in hips, shoulders, elbows, ankles, and other joints. These concepts can also be applied to the selection of non-articulating components of a device, where multiple components can be designed in relation to one-another based on either a patient-specific design, a selection of a best fit, or a combination thereof.
  • a femoral bearing surface can be derived off a tibial shape in one or more dimensions using the same or similar approaches.
  • a femoral head or humeral head bearing surface can be derived of an acetabulum or glenoid in one or more directions or the reverse.
  • the kinematics and wear of the implant can be optimized. For example, this approach can enhance the wear characteristics a polyethylene tibial insert. This approach also has some
  • any of the above embodiments are applicable to other joints and related implant components including an acetabulum, a femoral head, a glenoid, a humeral head, an ankle, a foot joint, an elbow including a capitellum and an olecranon and a radial head, and a wrist joint.
  • the position of pegs or keels or stems can be standard or can be patient specific or adapted based on the patient's anatomy.
  • a tibial component thickness can be selected, adapted or designed based on one or more of a patient's femoral or tibial AP or ML dimensions, femoral or tibial sagittal curvature, femoral or tibial coronal curvature, estimated contact area, estimated contact stresses, biomechanical loads, optionally for different flexion and extension angles, and the like. Both the metal thickness as well as the thickness of an optional insert can be selected, adapted or designed using this or similar information.
  • a femoral component thickness can be selected, adapted or designed based on one or more of a patient's femoral or tibial AP or ML
  • the surgeon can initially optimize the femoral and tibial resections. Optimization can be performed by measuring soft-tissue tension or ligament tension or balance for different flexion and extension angles or other joint positions before any bone has been resected, once a first bone resection on a first articular surface has been made and after a second bone resection on a first or second articular surface has been made, such as a femur and a tibia, humerus and a glenoid, femur and an acetabulum.
  • an acetabular component metal backed, ceramic or all plastic, e.g. polyethylene, or any other known in the art or developed in the future
  • a acetabular cup metal backed, ceramic or all plastic, e.g. polyethylene, or any other known in the art or developed in the future
  • reaming can be simulated for placement of an acetabular cup and the implant can then be designed or selected or adapted so that it will be closely matched to the resultant acetabular rim after reaming or other bone removal.
  • the exterior dimensions of the implant e.g. the rim and/or curvature(s) can be matched to the patient's geometry in this fashion. Curvatures of the exterior, bone facing shape of the acetabular cup can have constant or variable radii in one, two or three
  • acetabular component can be selected, adapted or designed to rest on the acetabular rim or extend beyond the acetabular rim, resting on portions of cortical bone or, for example, also osteophytes.
  • the acetabular fossa facing portion of the component can have standard dimensions, e.g. approximating those of a reamer used for reaming the acetabular fossa, while the peripheral portions, e.g.
  • those facing the acetabular rim or cortical bone e.g. on the acetabulum or ilium or ischium, can be patient specific or patient adapted. Any of these embodiments can be applicable to hip resurfacing techniques and implants as well as hip replacement techniques and implants.
  • the patient-specific data can be utilized to create a reaming guide or other tools for preparing the acetabular space for an implant component.
  • a guide or other tool that limits reamer motion or movement in various manners to one or more predetermined depths that were previously determined using patient-specific data, e.g. pre-operative CT or MRI or intraoperative ultrasound measurement of acetabular wall thickness.
  • Such a tool can comprise a patient-matched surface on the acetabulum and/or other acetabular head or other anatomical structures.
  • the tool can control both placement and depth of reaming tools to a desired degree.
  • the planning and design phase of such a guide tool can potentially identify any "at risk" operations for patients especially susceptible to such dangers, and possibly the implant design can be redesigned to accommodate the special needs of such patients as well.
  • a metal backed or ceramic acetabular component can include external, bone facing patient specific features and shapes, while the internal, insert facing shape can be standard.
  • a standard polyethylene insert can be locked into a patient specific acetabular cup; the acetabular cup has patient specific features or shapes on the external, bone facing side, while the internal dimensions or shape can be standard.
  • the external bone facing patient specific features and shape can help achieve a desired implant orientation and/or position including a desired anteversion or retroversion.
  • the internal dimensions can be standard and can be designed with a locking feature to hold a standard insert in place.
  • the standard insert locked into the acetabular metal backed or ceramic component can have a smooth, round internal bearing surface to accommodate a second insert and allow for rotation of the second insert within the first insert.
  • a femoral head component can rotate internal to the bearing surface of the insert.
  • the femoral head can be modular in design and it can, for example, be allowed to rotate on a mating femoral neck component.
  • the femoral neck component can, optionally, also be modular and can be selected for the patient's anatomy, e.g. using also an imaging test.
  • the femoral stem can be selected using an imaging test. The imaging test can be used to select a stem or neck component with any one of the following three geometries matched, adapted to or selected for the patient using one or more scan data:
  • an all polyethylene component or a metal backed component can be used.
  • the blank acetabular component can be aligned relative to the patient's acetabulum (optionally after a simulated surgical intervention, e.g., a reaming) to optimize the position of any standard attachment mechanisms relative to the bone to which they are intended to be attached.
  • the outer rim and, optionally, the bearing surface of the component can be adapted based on the patient's anatomy.
  • the outer periphery of the implant can be machined then to substantially align with portions of the patient's reamed acetabulum.
  • the length and width of the attachment mechanisms can be adapted to the thickness of the acetabular wall or to the existing bone stock available in the underlying and adjacent bone structures including the acetabular roof.
  • an acetabular component thickness can be selected, adapted or designed based on one or more of a patient's femoral or acetabular AP or ML or SI dimensions, femoral or acetabular sagittal curvature, femoral or acetabular coronal curvature, estimated contact area, estimated contact stresses, biomechanical loads, optionally for different flexion and extension angles, acetabular wall thickness and the like.
  • the metal, ceramic or plastic thickness as well as the thickness of an optional insert can be selected, adapted or designed using this or similar information.
  • the implant and related surgical instruments and surgical technique can include the following components, features and/or steps.
  • a patient specific mold can be generated based on the patient's image data, e.g., CT or MRI, ultrasound, laser imaging or combinations thereof or other imaging techniques available in the future.
  • the patient specific mold can include at least one surface that is at least partially shaped to be substantially a negative of an acetabular fossa.
  • the patient specific mold can be shaped to include shape features of the articular cartilage or subchondral bone or acetabular rim.
  • the patient specific shape of the mold can include shape information of osteophytes or geodes or cysts; alternatively, the patient specific shape of the mold can be shaped to avoid these structures or it can be corrected to a shape after removal of one or more of these structures.
  • the acetabular mold can be shaped to avoid contact with the ligamentum teres, the transverse acetabular ligament or the pulvinar; by avoiding contact with one or more of these structures, the spatial registration of the acetabular mold will be more accurate and will not lose accuracy of registration due to
  • the mold can fill portions or all of the acetabulum.
  • the mold can include various receptacles or guides for receiving various surgical instruments, including but not limited to drills, saws, and reamers.
  • the position and / or orientation of said one or more guides can be adapted based on the patient's anatomy, e.g.:
  • Femoral offset e.g., distance from femoral neck to center of femoral head
  • the mold can be adapted to other 2D or 3D parameters of the pelvis including, for example, lumbosacral angle, pelvic tilt, etc.
  • the mold can include a central guide for accepting a drill.
  • the guide can have a metal insert or bushing.
  • the central guide can be adapted to be at a predefined angle of abduction, e.g. 45 degrees, 40 degrees or 50 degrees, and / or anteversion, e.g. 20 degrees, 15 degrees, 10 degrees, 25 degrees, 30 degrees or 35 degrees.
  • a drill or a pin or other instrument is inserted into the guide and advanced into the acetabulum.
  • the drill or pin or instrument can define the center of the acetabulum.
  • the orientation of the drill or guide defines the desired acetabular cup orientation, e.g., with regards to abduction, anteversion, or rotation.
  • a reamer can optionally be inserted into the guide wherein the guide has a metal bushing and the reamer has a protrusion to fit into and rotate within the metal bushing.
  • the reamer can have an opening or hole that fits over a drill or pin that was previously placed in the acetabular fossa using the patient specific mold and guide. With this approach, the orientation of the reamer, e.g., with regards to acetabular abduction / adduction, ante-/retroversion, can be controlled, thereby ultimately controlling and achieving accurate placement of the acetabular cup.
  • surgeon can use an interactive computer display to select the desired acetabular cup abduction, adduction, anteversion, retroversion, rotation and other orientation, which is then transferred or translated into the position and orientation of one or more guides attached to or directly or indirectly linked to the mold.
  • the mold can have peripheral support features, e.g., anchors, screw attachments, lips or edges or other features that can help stabilize the mold against the pelvis. These support features can be inside or outside the acetabular fossa or combinations thereof.
  • the mold or at least portions of the mold, e.g., extra- acetabular support features, can remain in place while the reamer is reaming the acetabulum.
  • the reamer can be guided via the central acetabular hole or pin, but also via an external support, e.g., a metal cover on an extra- acetabular support structure.
  • the pin or instrument or metal bushing can be removed after reaming is complete.
  • overhanging bone can be removed prior to or after reaming to avoid iliopsoas or other tendon impingement.
  • the amount and location of bone removed can be determined via the same or another mold which is fitted to the acetabulum or extra-acetabular bone with one or more guide that allow insertion of a surgical instrument, e.g., a burr or reamer or saw, to remove such overhanging or other bone.
  • the acetabular cup can be spherical or aspherical, on the inside or the outside. The shape can be adapted to the patient's shape and anatomy in one or more dimensions.
  • the adaptation to the patient's shape can be in an AP, ML or SI direction, oblique directions or combinations thereof.
  • the outer shell of the acetabular cup is adapted to the patient's shape, including the shape after reaming or other surgical alteration thereby optimizing fixation to the underlying bone
  • the inner shape can be standard, for example, to accept a standard shape acetabular liner or insert.
  • the metal or ceramic facing portion of the insert can be patient specific in one or more dimensions, while the femoral head facing portion of the insert can have standard, fixed, predetermined radii, typically similar to or matching the radii of the femoral head component.
  • the acetabular cup can include fixation features inside the acetabular fossa, e.g., pegs or fins, as well as outside the acetabular fossa, e.g., extenders or plates with optional screw or other fixation.
  • the fixation features can be adapted to the patient using one or more patient specific features, e.g., bone stock subjacent to the acetabular cup, acetabular footplate, acetabular dimensions, and acetabular orientation.
  • the fixation features can further be adapted to achieve a
  • biomechanically superior solution for example by adapting peg or fin or other fixation angles relative to an acetabular abduction, adduction, anteversion, retroversion, or AP or ML placement selected by a surgeon, for example on a pre-operative
  • a mold or a feature created by a mold e.g., a hole or pin inserted into a hole, can be used to guide an impactor when impacting the acetabular cup for fixation.
  • the position and orientation of the mold or feature created by the mold can be optimized for changes induced by reaming or other surgical alteration.
  • the implant can have features that enhance cement interdigitation, e.g., cement pockets, surface features and the like.
  • the acetabular or femoral component can have features that allow for bone ingrowth, e.g. porous coating or other surface treatments.
  • the femoral component can be off-the-shelf, preformed or it can, optionally, include patient specific features.
  • the stem can have one or more dimensions adapted in shape to the femoral medullary cavity after reaming.
  • the stem can be off-the-shelf.
  • the neck portion can be affixed to the stem or it can be a modular neck that can be attached to the stem.
  • the neck, fixed or modular, can be available in different lengths and different anteversion, retroversion, abduction or adduction.
  • one or more of these features can be adapted to the patient intraoperatively or pre-operatively by shaping or selecting the
  • the articular surfaces may be patient-specific (i.e., femoral head diameter, etc.) or one or more dimensions may be engineered to reduce fatigue and wear (i.e., femoral head surface composition and/or design).
  • the neck length, width and offset e.g., distance from the femoral neck to the center of the femoral head, can optionally be patient specific or can be selected from pre-manufactured parts based on patient derived measurements, e.g., from a CT scan or MRI scan.
  • the femoral head, neck, shaft width/length/angle can be patient specific or can be selected from pre-manufactured parts based on patient derived measurements, e.g., from a CT scan or MRI scan.
  • One or more patient specific molds can be used for placing the femoral component.
  • a first mold can be placed against an uncut femoral neck with a guide that includes a predetermined orientation for guiding a saw blade and cutting the femoral neck at a desired angle and orientation in one or more dimensions.
  • a second mold can optionally be patient adapted and can be placed on top of the cut femoral neck or adjacent to the femoral neck with a guide to direct the orientation of a reamer for reaming the femoral medullary cavity.
  • FIGS. 46D and 46E depict a femoral head resurfacing implant 19605 for use in a hip resurfacing procedure.
  • a focused energy beam
  • the methods of crosslinking or otherwise altering the material properties of such implants can be incorporated into the components of almost any joint implant, including a medial condyle, a lateral condyle, a trochlea, a medial tibia, a lateral tibia, the entire tibia, a medial patella, a lateral patella, an entire patella, a medial trochlea, a central trochlea, a lateral trochlea, a portion of a femoral head, an entire femoral head, a portion of an acetabulum, an entire acetabulum, a portion of a glenoid, an entire glenoid, a portion of a humeral head, an entire humeral head, a portion of an ankle joint, an entire ankle joint, and/or a portion or an entire elbow, wrist, hand, finger, spine, or facet joint.
  • a glenoid component in a shoulder, can be designed or selected or adapted so that its peripheral margin will be closely matched to the patient specific glenoid rim or perimeter.
  • reaming can be simulated for placement of a glenoid component and the implant can then be designed or selected or adapted so that it will be closely matched to the resultant glenoid rim after reaming or other bone removal.
  • the exterior dimensions of the implant e.g. the rim and/or curvature(s) can be matched to the patient's geometry in this fashion.
  • Curvatures of the exterior, bone facing shape of the glenoid component can have constant or variable radii in one, two or three dimensions. At least one or more of these curvatures or surfaces can be adapted to the patient's shape in one or more dimensions, optionally adapted to the result of a simulated surgical alteration of the anatomy, e.g. reaming, the removal of
  • the implant can be adapted to the perimeter of the bone resulting after the cut has been placed.
  • at least a portion of the perimeter of the implant can be adapted to the perimeter of the patient's cut bone.
  • the undersurface of the implant can then be flat, facing the cut bone.
  • the glenoid component can be selected, adapted or designed to rest on the glenoid rim or extend beyond the glenoid rim, resting on portions of cortical bone or, for example, also osteophytes.
  • the glenoid fossa facing portion of the component can have standard dimensions, e.g.
  • peripheral portions e.g. those facing the glenoid rim or cortical bone, e.g. on the anterior or posterior aspect of the scapula
  • shoulder resurfacing techniques and implants as well as shoulder replacement techniques and implants, including primary and revision shoulder systems, as well as reverse or inverse shoulder systems.
  • the patient-specific data can be utilized to create a reaming guide or other tools for preparing the glenoid for an implant component.
  • a guide or other tool that limits reamer motion or movement in various manners to one or more predetermined depths that were previously determined using patient- specific data, e.g. pre-operative CT or MRI or intraoperative ultrasound measurement of glenoid depths.
  • Such a tool can comprise a patient-matched surface on the glenoid and/or other anatomical structures.
  • the tool can control both placement and depth of reaming tools to a desired degree.
  • the planning and design phase of such a guide tool can potentially identify any "at risk" operations for patients especially susceptible to such dangers, and possibly the implant design can be redesigned to accommodate the special needs of such patients as well.
  • a glenoid component can be selected for, adapted to or matched to the glenoid rim, optionally after surgically preparing or resectioning all or portions of the glenoid rim including osteophytes.
  • a metal backed or ceramic glenoid component can include external, bone facing patient specific features and shapes, while the internal, insert facing shape can be standard.
  • a standard polyethylene insert can be locked into a patient specific glenoid component; the glenoid component has patient specific features or shapes on the external, bone facing side, while the internal dimensions or shape can be standard.
  • the external bone facing patient specific features and shape can help achieve a desired implant orientation and/or position including a desired anteversion or retroversion.
  • the internal dimensions can be standard and can be designed with a locking feature to hold a standard insert in place.
  • the standard insert locked into the glenoid metal backed or ceramic component can have a smooth flat or concave bearing surface to articulate with a humeral head component.
  • the humeral head component can, optionally, be modular in design.
  • the humeral component can be selected for a patient, adapted to a patient or designed for a patient using an imaging test.
  • the imaging test can be used to select or adapt or design a shape with any one of the following three geometries matched, adapted to or selected for the patient using the one or more scan data:
  • a resurfacing humeral head component can be used with at least portions of a bone facing surface selected for, adapted to or designed for aspects of the patients humeral head shape.
  • a glenoid component an all polyethylene component can be used.
  • the blank glenoid component can be aligned relative to the patient's glenoid (optionally after a simulated surgical intervention) to optimize the position of any standard attachment mechanisms relative to the bone to which they are intended to be attached.
  • the outer rim and, optionally, the bearing surface of the component can be adapted based on the patient's anatomy.
  • the outer periphery of the implant can be machined then to substantially align with portions of the patients glenoid rim.
  • the length and width of the attachment mechanisms can be adapted to the mediolateral width of the glenoid or to the existing bone stock available or any other glenoid dimension, e.g. superoinferior.
  • the articular surface of a glenoid component can have a standard geometry in one or more dimensions or can be completely standard.
  • the articular surface of the glenoid component can also include patient specific or patient derived shapes.
  • the articular surface of the glenoid component can be derived using the curvature or shape of the cartilage or subchondral bone of the patient, on the glenoid or the humeral side, in one or more dimensions or directions.
  • the articular surface of a humeral component can be derived using the curvature or shape of the cartilage or subchondral bone of the patient on the humerus or glenoid in one or more dimensions or directions and the articular surface of the glenoid component can be selected or adapted or designed based on the humeral component implant shape.
  • the selection, adaption or design can occur using a set of rules, e.g. desirable humeral to glenoid articular surface radius ratios, in one or more planes, e.g. superoinferior or mediolateral.
  • the foregoing is applicable to any other joint in the body including knees, hips, ankles, elbows and wrists.
  • a glenoid component thickness can be selected, adapted or designed based on one or more of a patient's humeral or glenoid AP or ML or SI dimensions, humeral or glenoid sagittal curvature, humeral or glenoid coronal curvature, estimated contact area, estimated contact stresses, biomechanical loads, optionally for different flexion and extension angles, glenoid bone stock and the like.
  • the metal, ceramic or plastic thickness as well as the thickness of an optional insert can be selected, adapted or designed using this or similar information.
  • one or more sets of jigs can be designed to facilitate and accommodate surgical procedures on bones and joint other than the knee.
  • the jigs are designed in connection with the design of a patient-specific implant component.
  • the designed jigs guide the surgeon in performing one or more patient- specific cuts to the bone so that those cut bone surface(s) negatively-match the patient-specific bone cuts of the implant component.
  • FIG. 47A depicts a normal humeral head and upper humerus which forms part of a shoulder joint.
  • FIG. 47B depicts the humeral head having an alignment jig designed to identify and located various portions of the humeral anatomy.
  • a jig having a plurality of conforming surfaces has been designed using patient-specific information regarding one or more of the humerus, the humeral neck, the greater tuberosity and/or the lesser tuberosity of the humerus.
  • the conforming surfaces will fit onto the humerus on only one position and orientation, thereby aligning to the humerus in a known position.
  • This embodiment desirably incorporates an alignment hole 18400 which aligns with an axis 18410 of the humeral head.
  • a pin or other mechanism i.e., drill, reamer, etc.
  • drill, reamer, etc. can be inserted into the hole 18400, and provide a secure reference point for various surgical operations, including the reaming of the humeral head and/or drilling of the axis 18400 in preparation for a humeral head resurfacing implant or other surgical procedure.
  • the alignment mechanisms may be connected to the one or more conforming surfaces by linkages (removable, moveable and/or fixed) or other devices, or the entire jig may be formed from a single piece and extend over a substantial portion of the humeral head and/or other bone.
  • FIG. 47C depicts an alternative embodiment of a humeral head jig that utilizes a single conforming surface to align the jig.
  • one or more protrusions or osteophytes is mirrored by the conforming surfaces, which permits alignment and positioning of the jig in a known manner.
  • FIG. 48A depicts a humeral head with osteophytes
  • FIGS. 48B and 48C depict the humeral head with a more normalized surface that has been corrected by virtual removal of the osteophytes
  • FIG. 49A depicts a humeral head with voids, fissures or cysts
  • FIGS. 49B and 49C depict the humeral head with a more normalized surface that has been corrected by virtual removal of the voids, fissures or cysts.
  • FIG. 50A depicts a health scapula of a shoulder joint
  • FIG. 50B depicts a normal glenoid component of the shoulder
  • FIG. 50C depicts an alignment jig for use with the glenoid.
  • the jig may comprise one or more conforming surfaces that are shaped to mirror the patient-specific anatomy of the glenoid, allowing the jig to be positioned on the glenoid in a known position and orientation.
  • An alignment hole 18450 in the glenoid jig provides a desired pathway for orienting and inserting a pin or other alignment mechanism, or provide a pathway for a drilling or reaming device.
  • the jig can be removed and the pin utilized as a secure reference point for various surgical operations, including the milling and/or reaming of the glenoid in preparation for a glenoid component of a shoulder joint replacement/resurfacing implant (see FIG. 50D).
  • FIG. 51 A depicts a glenoid component with osteophytes
  • FIG. 51 B depicts the glenoid component with a more normalized surface that has been corrected by virtual removal of the osteophytes
  • FIGS. 51 C and 51 D depict two alternative embodiments of a glenoid jig for use with the glenoid, each of which incorporates conforming surfaces that accommodate the osteophytes.
  • the jig of FIG. 51 C can be formed from an elastic or flexible material to allow it to "snap fit" over the glenoid component and associated osteophytes.
  • the jigs can include various alignment holes, slots, etc., to allow placement of pins or other surgical actions.
  • FIG. 52A depicts a glenoid component with voids, fissures or cysts
  • FIG. 52B depicts the glenoid component with a more normalized surface that has been corrected by virtual "filling" of the voids, fissures or cysts
  • FIG. 52C depicts an embodiment of a glenoid jig for use with the glenoid component, which incorporates various conforming surfaces that accommodate the voids, fissures and/or cysts (and other surfaces) of the glenoid component.
  • a talar or tibial component in an ankle joint, can be designed or selected or adapted so that its peripheral margin will be closely matched to the patient specific bony rim or perimeter in one or two or more dimensions.
  • reaming or cutting can be simulated for placement of a component and the implant can then be designed or selected or adapted so that it will be closely matched to the resultant bony contour or surface after reaming or cutting or other bone removal.
  • the exterior dimensions of the implant e.g.
  • the rim and/or curvature(s) can be matched to the patient's geometry in this fashion.
  • Curvatures of the exterior, bone facing shape of the talar or tibial component can have constant or variable radii in one, two or three dimensions. At least one or more of these curvatures or surfaces can be adapted to the patient's shape in one or more dimensions, optionally adapted to the result of a simulated surgical alteration of the anatomy, e.g. reaming, the removal of osteophytes or cutting.
  • the implant can be adapted to the perimeter of the bone resulting after the cut has been placed. In this setting, at least a portion of the perimeter of the implant can be adapted to the perimeter of the patient's cut bone.
  • the undersurface of the implant can then be flat, facing the cut bone.
  • the tibial or talar component can be selected, adapted or designed to rest on the bony rim or surface or extend beyond the bony rim of the articular surface, resting on portions of cortical bone or, for example, also osteophytes.
  • the articular bone facing portion of the component can have standard dimensions, e.g. approximating those of a reamer used for reaming the bone, while the peripheral portions, e.g. those facing the bony rim or cortical bone, e.g. on the anterior tibia or lateral or medial aspect of the talus, can be patient specific or patient adapted. Any of these embodiments can be applicable to ankle resurfacing techniques and implants as well as ankle replacement techniques and implants, including primary and revision ankle systems.
  • a humeral or radial or ulnar component in an elbow joint, can be designed or selected or adapted so that its peripheral margin will be closely matched to the patient specific bony rim or perimeter in one or two or more dimensions.
  • reaming or cutting can be simulated for placement of a component and the implant can then be designed or selected or adapted so that it will be closely matched to the resultant bony contour or surface after reaming or cutting or other bone removal.
  • the exterior dimensions of the implant e.g.
  • the rim and/or curvature(s) can be matched to the patient's geometry in this fashion.
  • Curvatures of the exterior, bone facing shape of the humeral or radial or ulnar component(s) can have constant or variable radii in one, two or three dimensions. At least one or more of these curvatures or surfaces can be adapted to the patient's shape in one or more dimensions, optionally adapted to the result of a simulated surgical alteration of the anatomy, e.g. reaming, the removal of osteophytes or cutting. For example, if a cut is performed, the implant can be adapted to the perimeter of the bone resulting after the cut has been placed.
  • the perimeter of the implant can be adapted to the perimeter of the patient's cut bone.
  • the undersurface of the implant can then be flat, facing the cut bone.
  • the humeral or radial or ulnar component(s) can be selected, adapted or designed to rest on the bony rim or surface or extend beyond the bony rim of the articular surface, resting on portions of cortical bone or, for example, also osteophytes.
  • the articular bone facing portion of the component can have standard dimensions, e.g. approximating those of a reamer used for reaming the bone, while the peripheral portions, e.g. those facing the bony rim or cortical bone, e.g. on the anterior humerus or lateral or medial aspect of the radius or ulna, can be patient specific or patient adapted. Any of these embodiments can be applicable to elbow resurfacing techniques and implants as well as elbow
  • a radial or ulnar or scaphoid or lunate component in a wrist joint, can be designed or selected or adapted so that its peripheral margin will be closely matched to the patient specific bony rim or perimeter in one or two or more dimensions.
  • reaming or cutting can be simulated for placement of a component and the implant can then be designed or selected or adapted so that it will be closely matched to the resultant bony contour or surface after reaming or cutting or other bone removal.
  • the exterior dimensions of the implant e.g.
  • the rim and/or curvature(s) can be matched to the patient's geometry in this fashion.
  • Curvatures of the exterior, bone facing shape of the radial or ulnar or scaphoid or lunate component(s) can have constant or variable radii in one, two or three dimensions. At least one or more of these curvatures or surfaces can be adapted to the patient's shape in one or more dimensions, optionally adapted to the result of a simulated surgical alteration of the anatomy, e.g. reaming, the removal of osteophytes or cutting. For example, if a cut is performed, the implant can be adapted to the perimeter of the bone resulting after the cut has been placed.
  • the perimeter of the implant can be adapted to the perimeter of the patient's cut bone.
  • the undersurface of the implant can then be flat, facing the cut bone.
  • the radial or ulnar or scaphoid or lunate component(s) can be selected, adapted or designed to rest on the bony rim or surface or extend beyond the bony rim of the articular surface, resting on portions of cortical bone or, for example, also osteophytes.
  • the articular bone facing portion of the component can have standard dimensions, e.g.
  • peripheral portions e.g. those facing the bony rim or cortical bone, e.g. on the anterior radius
  • wrist resurfacing techniques and implants as well as wrist replacement techniques and implants, including primary and revision wrist systems.
  • important considerations in the selection and/or design of patient-specific implant components, tools and surgical procedures can include various factors relevant to the manufacture and/or modification of implant components, tools and associated surgical components for use in the surgical procedure. This is especially relevant where the implant components have not been pre-manufactured and stockpiled in a final usable form, or where selected component blanks and/or tools require additional modifications prior to use.
  • Designing and/or selecting an implant component and/or guide tool as described herein can include both configuring one or more features, measurements, and/or dimensions of the implant and/or guide tool (e.g., derived from patient-specific data from a particular patient and adapted for the particular patient) and
  • manufacturing can include making the implant component and/or guide tool from starting materials, for example, metals and/or polymers or other materials in solid (e.g., powders or blocks) or liquid form.
  • manufacturing can include altering (e.g., machining) an existing implant component and/or guide tool, for example, a standard blank implant component and/or guide tool or an existing implant component and/or guide tool (e.g., selected from a library).
  • manufacturing techniques to making or altering an implant component and/or guide tool can include any techniques known in the art today and in the future. Such techniques include, but are not limited to additive as well as subtractive methods, i.e., methods that add material, for example to a standard blank, and methods that remove material, for example from a standard blank.

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Abstract

La présente invention concerne des procédés et des dispositifs concernant des modèles articulaires améliorés, des composants d'implants, et des outils de guidage et des procédures associés. De plus, l'invention concerne des procédés et des dispositifs concernant des modèles articulaires, des composants d'implants, et/ou des outils de guidage et des procédures associés comprenant une ou plusieurs caractéristiques dérivées des données relatives aux patients, par exemple, des images de l'articulation du patient. Les données peuvent être utilisées pour créer un modèle d'analyse d'une articulation d'un patient et pour concevoir et évaluer le cours d'une action correctrice. Les données peuvent également être utilisées pour créer des composants d'implants adaptés aux patients et des outils et des procédures associés.
PCT/US2012/025274 2011-02-15 2012-02-15 Implants articulaires adaptés à un patient et améliorés, procédures et outils destinés à déterminer, évaluer, corriger, modifier et/ou s'adapter à une variation et/ou à une asymétrie anatomique WO2012112698A2 (fr)

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AU2012217654A AU2012217654B2 (en) 2011-02-15 2012-02-15 Patient-adapted and improved articular implants, procedures and tools to address, assess, correct, modify and/or accommodate anatomical variation and/or asymmetry
CN201280018695.5A CN103476363B (zh) 2011-02-15 2012-02-15 改进的适合患者型关节植入物以及处理、评估、校正、修改和/或适应解剖变化和/或非对称性的手术和工具

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US61/443,155 2011-02-15

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PCT/US2012/025269 WO2012112694A2 (fr) 2011-02-15 2012-02-15 Modélisation, analyse et utilisation de données anatomiques d'implants adaptés à des patients, conception, outils et procédures chirurgicales
PCT/US2012/025277 WO2012112701A2 (fr) 2011-02-15 2012-02-15 Implants articulaires améliorés et adaptés aux patients, conceptions, procédures chirurgicales et outils de guidage correspondants
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PCT/US2012/025277 WO2012112701A2 (fr) 2011-02-15 2012-02-15 Implants articulaires améliorés et adaptés aux patients, conceptions, procédures chirurgicales et outils de guidage correspondants
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AU2012217654B2 (en) 2016-09-22
WO2012112694A2 (fr) 2012-08-23
WO2012112701A3 (fr) 2013-01-17
WO2012112702A3 (fr) 2013-01-17
SG193484A1 (en) 2013-10-30
US20120209394A1 (en) 2012-08-16
US10456263B2 (en) 2019-10-29
CN103476363A (zh) 2013-12-25
WO2012112702A2 (fr) 2012-08-23
WO2012112701A2 (fr) 2012-08-23
CN103476363B (zh) 2017-06-30
US20160143744A1 (en) 2016-05-26
EP2754419B1 (fr) 2024-02-07
WO2012112698A3 (fr) 2013-03-14
EP2754419A2 (fr) 2014-07-16
US9020788B2 (en) 2015-04-28
WO2012112694A3 (fr) 2013-01-03
EP2754419A3 (fr) 2014-10-08
AU2012217654A1 (en) 2013-10-03

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